US20120179162A1 - Inflatable medical devices - Google Patents
Inflatable medical devices Download PDFInfo
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- US20120179162A1 US20120179162A1 US13/293,058 US201113293058A US2012179162A1 US 20120179162 A1 US20120179162 A1 US 20120179162A1 US 201113293058 A US201113293058 A US 201113293058A US 2012179162 A1 US2012179162 A1 US 2012179162A1
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- United States
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- pusher
- length
- tube
- target site
- flexible tube
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/70—Spinal positioners or stabilisers ; Bone stabilisers comprising fluid filler in an implant
- A61B17/7097—Stabilisers comprising fluid filler in an implant, e.g. balloon; devices for inserting or filling such implants
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
- A61B17/8802—Equipment for handling bone cement or other fluid fillers
- A61B17/8805—Equipment for handling bone cement or other fluid fillers for introducing fluid filler into bone or extracting it
- A61B17/8816—Equipment for handling bone cement or other fluid fillers for introducing fluid filler into bone or extracting it characterised by the conduit, e.g. tube, along which fluid flows into the body or by conduit connections
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
- A61B17/8802—Equipment for handling bone cement or other fluid fillers
- A61B17/8805—Equipment for handling bone cement or other fluid fillers for introducing fluid filler into bone or extracting it
- A61B17/8822—Equipment for handling bone cement or other fluid fillers for introducing fluid filler into bone or extracting it characterised by means facilitating expulsion of fluid from the introducer, e.g. a screw pump plunger, hydraulic force transmissions, application of vibrations or a vacuum
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
- A61B17/8802—Equipment for handling bone cement or other fluid fillers
- A61B17/8805—Equipment for handling bone cement or other fluid fillers for introducing fluid filler into bone or extracting it
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
- A61B17/8802—Equipment for handling bone cement or other fluid fillers
- A61B17/8805—Equipment for handling bone cement or other fluid fillers for introducing fluid filler into bone or extracting it
- A61B17/8808—Equipment for handling bone cement or other fluid fillers for introducing fluid filler into bone or extracting it with sealing collar for bone cavity
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
- A61B17/8802—Equipment for handling bone cement or other fluid fillers
- A61B17/8805—Equipment for handling bone cement or other fluid fillers for introducing fluid filler into bone or extracting it
- A61B17/8811—Equipment for handling bone cement or other fluid fillers for introducing fluid filler into bone or extracting it characterised by the introducer tip, i.e. the part inserted into or onto the bone
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C5/00—Filling or capping teeth
- A61C5/60—Devices specially adapted for pressing or mixing capping or filling materials, e.g. amalgam presses
- A61C5/62—Applicators, e.g. syringes or guns
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/46—Special tools or methods for implanting or extracting artificial joints, accessories, bone grafts or substitutes, or particular adaptations therefor
- A61F2/4601—Special tools or methods for implanting or extracting artificial joints, accessories, bone grafts or substitutes, or particular adaptations therefor for introducing bone substitute, for implanting bone graft implants or for compacting them in the bone cavity
Definitions
- Devices and methods for a delivering a material into an orthopedic target site are disclosed.
- devices and methods for delivering bone cement to a vertebral body are disclosed.
- bone cement is injected to stabilize a vertebral compression fracture.
- a balloon is first inserted into a vertebral body and inflated to create a void. The void is then filled with bone cement.
- Some devices for moving bone cement consist of a hand pump and a flexible tube.
- the tube is inserted into the orthopedic structure and bone cement is pumped through the tube and into the structure.
- the tube is long enough that the pump may be located up to several feet from the injection site.
- These devices have the advantage of allowing the physician to be removed from the injection site such that he or she is not exposed to the x-rays used to guide the filling procedure.
- tactile feedback is poor, excessive pressures can be generated and the bone cement remaining in the tube is all wasted in the end. Detaching the tube from the mass of injected bone cement can also be problematic.
- Some devices such as those used for kyphoplasty, use a simple rigid hollow tube with a solid rigid pusher rod that slides down the tube.
- the hollow tube is filled with bone cement and the solid pusher rod drives the bone cement into the body.
- These devices have the advantage of excellent tactile feedback, simplicity, lack of waste and easy termination with the mass of injected bone cement.
- they have small volumes and, because they are used right at the injection site, may expose the physician to x-rays during the filling procedure.
- they may require significant force to extrude cement as the cement hardens.
- What is needed is a device to place material into bone that protects physicians from X-ray exposure, has adequate volume, smooth operation, good haptics, minimizes waste and allows easy termination with the mass of injected bone cement.
- a device for delivering a material into an orthopedic target site can have a flexible tube having a first lumen having a first end and a second end.
- the first lumen can extend along all or part of the length of the flexible tube.
- the device can have a pusher having a pusher total length.
- the pusher can have a pusher first length along and a pusher second length.
- the pusher first length can abut or contact the pusher second length.
- the pusher first length can have a first rigidity.
- the pusher second length can have a second rigidity.
- the first rigidity can be less than or greater than the second rigidity.
- the pusher and tube can be configured for the pusher to be slidably received by a port at the proximal end of the first lumen.
- the material to be delivered can be located in the first lumen between the pusher and the distal end of the flexible tube.
- the pusher first length can be at least about 10% of the pusher total length.
- the pusher second length can be at least about 10% of the pusher total length.
- the material can be or have a bone cement.
- the flexible tube can have a low friction material configured to resist binding to the bone cement.
- the flexible tube can be translucent and/or transparent.
- the flexible tube can have a second lumen along all or part of the length of the flexible tube.
- the pusher second length can have a cable.
- a method for delivering a material into an orthopedic target site can include slidably positioning a pusher into a first lumen of a flexible tube.
- the first lumen can have a first port and a second port.
- the pusher can have a pusher first length and a pusher second length.
- the pusher first length can be more rigid or less rigid than the pusher second length.
- the method can include loading the first lumen with the material between the pusher second length and the second port.
- the method can include positioning the flexible tube so the flexible tube is configured to have at least a first curve, for example to navigate around an anatomical obstruction. Positioning the flexible tube can include the second port being located at the orthopedic target site.
- the method can include moving the pusher from a first pusher position to a second pusher position. Moving the pusher from the first pusher position to the second pusher position can include moving the pusher second length across the first curve.
- the method can include deploying the material from the lumen to the orthopedic target site.
- the deploying of the material is concurrent with the moving of the pusher from the first pusher position to the second pusher position.
- the material to be delivered to the orthopedic target site can be or have a bone cement.
- the method can include stopping a flow of the material.
- the stopping of the flow can include ceasing a translational movement of the pusher with respect to the flexible tube.
- the method can include removing the flexible tube from the orthopedic target site.
- the method can include creating a void at the orthopedic target site.
- the method can include positioning a cannula at the orthopedic target site.
- the cannula can have a cannula distal port open to the orthopedic target site once the cannula is positioned.
- Positioning the flexible tube can include moving the flexible tube through the cannula, for example, until the distal port of the flexible tube exits the cannula distal port.
- a method for delivering a material into an orthopedic target site can include positioning a device at the orthopedic target site.
- the pusher or advancement rod can have an advancement rod first length and an advancement rod second length.
- the advancement rod first length can have a different rigidity than a rigidity of the advancement rod second length.
- the method can include advancing the advancement rod from an advancement rod proximal position to an advancement rod distal position. During the advancing of the advancement rod, the first length of the advancement rod can be non-collinear with the advancement rod second length.
- the method can include deploying the material from the device to the orthopedic target site.
- the material can be deployed preceding, subsequent to, concurrent with, or combinations thereof, the advancing of the advancement rod.
- FIG. 1 illustrates a variation of a void creation tool.
- FIG. 2 a illustrates a variation of the material delivery device.
- FIGS. 2 b and 2 c are cross-sections B-B and C-C, respectively, of a variation of the device.
- FIGS. 2 d and 2 e are cross-sections B-B and C-C, respectively, of a variation of the device.
- FIG. 3 illustrates a variation of the device dissembled.
- FIG. 4 illustrates a variation of the delivery device inner assembly in a curved configuration.
- FIG. 5 illustrates a variation of the delivery device outer assembly in a curved configuration.
- FIG. 6 is a close-up cross-section of a length of the device.
- FIG. 7 is a close-up view of a length of a variation of the device.
- FIG. 8 is a close-up view of a length of a variation of the proximal end of the device.
- FIG. 9 is a close-up view of a length of a variation of the distal end of the device.
- FIGS. 10A through 10E illustrate variations of cross-section A-A.
- FIGS. 11 a and 11 b are close-up, phantom views of variations of the distal end of the device.
- FIGS. 12 a and 12 b illustrate a variation of a method for controllably closing the distal end of the device.
- FIGS. 13 a and 13 b illustrate a variation of a method for controllably closing the distal end of the device.
- FIGS. 14 a and 14 c illustrate a variation of a method for controllably opening and closing the distal end of the device.
- FIG. 15 is a sagittal section of a patient including a full view of a spine.
- FIG. 16 is a close-up transverse section of a patient including a vertebra and the adjacent nerves including the spinal cord.
- FIGS. 17A through 17 i illustrate a method for creating one or more voids at a target site within a vertebral body, filling the voids with a filler material such as bone cement, and withdrawing surgical tools for creating the voids and delivering the filler material from the target site.
- a filler material such as bone cement
- FIG. 18 is a graph showing pressure verse diameter for variations of balloons including burst pressures.
- FIGS. 19 and 20 illustrate methods for using the delivery device.
- FIG. 1 illustrates that an inflation system 470 can have an expandable void-creation volume such as balloon 20 that can be inflated by pushing inflation fluid, such as water, saline, a gel or dye, from the syringe 472 , into the inflation port 482 , through the hollow shaft lumen 154 and into the balloon 20 .
- inflation fluid such as water, saline, a gel or dye
- the syringe 472 can be detachable or non-detachable from the remainder of the inflation system 470 .
- the stiffening rod 474 can be removed from the inflation system 470 or left in place to stiffen the inflation system 470 while positioning the balloon 20 in the body.
- the stiffening rod tip 484 can have atraumatic geometry, or a soft plastic or elastomeric tip that will minimize puncture or damage the distal end of the balloon.
- the inflation system 470 can have a stiffening rod control 480 , for example a knob or handle on the proximal end of the inflation system 470 to control the position of the stiffening rod 474 .
- a seal 286 adjacent to the stiffening rod control can prevent pressure from escaping from the hollow shaft lumen.
- FIG. 2 a illustrates a delivery service or system that may be used to deliver a material, such as one or more bone cements, morselized bone, or combinations thereof, into the body.
- Cement delivery device 996 may be comprised of cement delivery device outer assembly 1000 and cement delivery device inner assembly 1008 .
- Inner assembly 1008 may be inserted into outer assembly 1000 such that the inner assembly 1008 can slide relative to the outer assembly 1000 .
- FIG. 3 shows that the cement delivery device outer assembly 1000 may comprise outer assembly tube 1002 , outer assembly handle 1004 , outer assembly tube end 1006 with an outer assembly tube end length 1007 and bone cement filling fitting 1032 .
- Outer assembly tube 1002 may be comprised of a low-friction material such as PTFE, LDPE or the like.
- tube 1002 may be made of a material that has a dynamic coefficient of friction with steel of less than 0.3, more narrowly less than 0.2, still more narrowly less than 0.1.
- the low-friction material can resist binding to the bone cement.
- Outer assembly tube 1002 may be flexible, rigid, semi-flexible, or combinations thereof, for example alternating along the length of the outer assembly tube 1002 .
- Outer assembly tube 1002 may be opaque, clear, transparent, translucent or combinations thereof.
- Outer assembly tube 1002 may comprise a fiber reinforcement element, such as a braid. This fiber reinforcement element may increase radial stiffness when the tube 1002 is pressurized.
- Outer assembly tube 1002 may have an outer diameter of less than about 0.32 inches (8.1 mm), more narrowly less than 0.2 inches (5 mm).
- Outer assembly tube 1002 may have a length of 12-32 inches (304-813 mm).
- Outer assembly tube 1002 may have about a 0.138 inch (3.50 mm) outer diameter and about a 0.108 inch (2.74 mm) inner diameter and about a length of 20 inches (508 mm).
- FIG. 3 shows that the cement delivery device inner assembly 1008 may comprise an inner assembly pushing device 1014 and an inner assembly handle 1012 .
- Pusher, advancement rod, or inner assembly pushing device 1014 may comprise a pushing device rigid portion 1020 with a pushing device rigid portion length 1028 , and a pushing device flexible portion 1016 with a pushing device flexible portion length 1024 and a pushing device flexible portion tip 1018 .
- the pushing device rigid portion length 1028 can be about 10% or more, or yet more narrowly greater than or equal to about 25%, for example about 65% of the entire length of the inner assembly pushing device 1014 .
- the pushing device flexible portion length 1024 can be about 10% or more, or, yet more narrowly greater than or equal to about 25%, or for example about 35% of the entire length of the inner assembly pushing device 1014 .
- the pushing device rigid portion length 1028 and the pushing device flexible portion length 1024 can combine to be about the entire length of the inner assembly pushing device 1014 .
- the pushing device rigid portion 1020 can abut, be integral with, or contact the pushing device flexible portion 1016 .
- the pushing device flexible portion 1016 can be a cable fused, hound, clipped, wedged into a port in the distal end of the pushing device rigid portion 1020 , or combinations thereof.
- the pushing device rigid portion 1020 may be a rod or a tube or a semi-rigid cable with an outside diameter of about 0.050-0.090 inches (1.27-2.29 mm).
- the pushing device rigid portion length 1028 may be about 7-15 inches (178-381 mm).
- the pushing device flexible portion 1016 may be a semi-rigid cable or semi-flexible cable with a diameter of about, 0.040-0.080 inches (1.02-2.03 mm), more narrowly 1/16 of an inch (1.59 mm).
- the pushing device flexible portion 1016 may be attached to the pushing device rigid portion 1020 by a bond, a crimp, a weld, a braze or some combination thereof.
- the pushing device flexible portion length 1024 may be about 1-7 inches (25-178 mm).
- the pushing device flexible portion tip 1018 may be comprised of an additional short section of tubing, a tightly bonded termination of the cable, a crimp fitting, or combinations thereof.
- the pushing device flexible portion 1016 may be omitted entirely from the inner assembly pushing device 1014 .
- FIGS. 2 b and 2 c illustrate a variation of cross-sections B-B and C-C respectively.
- FIG. 2 b illustrates that the tube 1002 can have a lumen 1100 .
- the tube 1002 can have multiple, separated lumens.
- the lumen 1100 can extend all or a part of the length of the tube 1002 .
- the pushing device rigid portion length 1028 the pushing device rigid portion 1020 of the inner assembly 1008 can have a uniform solid or hollow circular cross-section.
- FIG. 2 c illustrates that along the pushing device flexible portion length 1024 , the pushing device flexible portion 1016 of the inner assembly 1008 can be porous, woven and/or braided, for example, as a cable.
- the diameter of the pushing device rigid portion 1020 can be greater than, equal to, or less than the diameter of the pushing device flexible portion 1016 .
- the gap between the radially inner surface of the tube 1002 and the radially outer surface of the pushing device rigid portion 1020 and/or the pushing device flexible portion 1016 can be nominal (e.g., sufficient to allow sliding), or large enough to allow deployment delivery of bone cement or other materials through the gap.
- FIGS. 2 d and 2 e illustrate a variation of cross-sections B-B and C-C respectively.
- FIG. 2 d illustrates that along the pushing device rigid portion length 1028 the pushing device rigid portion 1020 of the inner assembly 1008 can have a circular cross-section or cylindrical core 1102 .
- the core 1102 can be radially surrounded by a solid or cabled stiffening sheath 1104 .
- the core 1102 can have a smaller radius than the stiffening sheath 1104 .
- the core can be made from the same material 1102 or a different material than the sheath 1104 .
- FIG. 2 e illustrates that along the pushing device flexible portion length 1024 , the pushing device flexible portion 1016 of the inner assembly 1008 can have the core 1102 , for example unsurrounded by the stiffening sheath 1104 .
- FIG. 4 shows that flexible portion 1016 may be bent to form an angle 1092 by applying a force 1088 normal to the longitudinal axis of flexible portion 1016 using, for instance, operator hand 1084 .
- Angle 1092 may be greater than about 45 degrees, more narrowly greater than about 90 degrees.
- Force 1088 may be less than 30 newtons, more narrowly less than 15 newtons, more narrowly less than 5 newtons, still more narrowly less than 2.5 newtons
- pushing device flexible portion length may 1024 may be about 3 inches long, force 1088 may be about 1 newton and angle 1092 may be about 90 degrees. Applying and then removing force 1088 to flexible portion 1016 may not result in any significant permanent deformation in the shape of flexible portion 1016 .
- the flexible portion 1016 can be straight and/or bend having a radius of curvature of greater than or equal to about 4 in., more narrowly about 3 in, yet more narrowly about 1 in.
- the tube 1002 for example along the length at which the flexible portion 1016 is positioned, can curve to a radius of curvature about equal to the radius of curvature of about the radius of curvature of the flexible portion 1016 , e.g., being straight, having a radius of curvature of greater than or equal to about 4 in., more narrowly about 3 in, yet more narrowly about 1 in.
- FIG. 5 shows that outer assembly 1000 can be flexible.
- tube 1002 can be deformed into a circle without any significant permanent deformation.
- FIG. 6 shows the pushing device flexible portion 1016 and the pushing devise flexible portion tip 1018 sliding within outer assembly tube 1002 . As shown, pushing device flexible portion 1016 and the pushing device flexible portion tip 1018 may be visible through the walls of outer assembly tube 1002 .
- FIG. 7 shows that outer assembly tube 1002 may be made in a curved or spiral shape.
- Outer assembly tube 1002 may comprise a tube reinforcement spring 1036 wrapped around the outside diameter of the tube.
- Spring 1036 may make tube 1002 stiffer and/or give tube 1002 a higher burst pressure.
- FIG. 8 shows outer assembly handle 1004 and bone cement filling fitting 1032 attached to outer assembly tube 1002 .
- Bone cement filling fitting 1032 may be, for instance, a luer fitting.
- FIG. 9 shows a possible configuration of the outer assembly tube end 1006 .
- Tube end 1006 may be a fitting with a smaller inside diameter than outer assembly tube 1002 .
- Tube end 1006 can be a straight rigid tube.
- Outer assembly tube end 1006 may be made of a material that bonds well to bone cement. For instance, it could be made of a metal, or a porous material that bone cement may flow into.
- FIGS. 10A-E show variations of cross-section A-A of outer assembly tube end 1006 .
- Tube end 1006 can have one or more vanes 1040 that extend over all or part of the length 1007 of tube end 1006 .
- the vanes can furcate (e.g., bifurcate, trifurcate, quadfurcate) the tube end 1006 or entire tube 1008 into multiple lumens.
- Vanes 1040 maybe made of a material that forms a strong bond with bone cement. Vanes 1040 may increase the area available for bone cement to bond in tube end 1006 , thus increasing bond strength.
- Tube end 1006 may be solid except for holes 1042 that pass lengthwise through end 1006 .
- tube end 1006 may have 1, 2, 3, 4, 5, more than 5, more than 10 or more than 50 lengthwise holes 1042 .
- Each hole 1042 can be in fluid communication with a single lumen in the tube or each hole 1042 can be in communication with separate lumens in the tube.
- FIGS. 11 a and 11 b show tube 1002 with tube end 1006 .
- Tube end 1006 is, for instance, a plug which half covers the exits of tube 1002 .
- Inner tube 1076 is sized to pass thru the inner diameter of tube 1002 and has and end plug which covers about half the exit of inner tube 1076 .
- material may exit tube 1002 at tube end 1006 .
- FIG. 11 b material is blocked from exiting tube 1002 .
- the distal end of tube 1002 may be closed. This closing may serve to sever tube end 1006 from the material immediately distal to tube end 1006 .
- FIGS. 12 a - 12 b shows a material flow valve 1048 .
- the valve 1048 may consist of a circular flapper mounted on a pivot. In FIG. 12 a , the flapper is turned vertically allowing material to flow. In FIG. 12 b , the flapper is turned horizontally, stopping the flow of material.
- FIGS. 13 a - 13 b show that outer assembly tube 1002 can be circumferentially closed by pulling cable 1044 .
- FIGS. 14 a - 14 c show a material flow valve that is activated passively.
- bone cement 445 is flowing towards cement flow valve 1048 .
- FIG. 14 b the bone cement 445 has reached cement flow valve 1048 and the back pressure on the bone cement 445 has caused cement flow valve 1048 to open.
- FIG. 14 c the back pressure on the bone cement 445 is now not sufficient to hold cement flow valve 1048 open and it closes automatically.
- FIG. 15 illustrates a sagittal view of a patient and the spine 406 .
- the spine 406 can have vertebrae 408 and cervical, thoracic, lumbar and sacral regions 410 , 412 , 414 , and 416 .
- the device 470 and 996 can be used in or between vertebrae 408 in any region of the spine 406 .
- FIG. 16 illustrates a vertebrae 408 that can have cortical bone 418 and cancellous bone 420 .
- the vertebrae 408 can have a vertebral body 422 a vertebral process 424 and pedicles 426 .
- FIGS. 17A through 17 i illustrate a method for deploying balloons 20 bilaterally, for example including one balloon inserted through each of opposing pedicles 426 a and 426 b.
- FIG. 17A illustrates that a first delivery tube 428 a , such as a cannula, can be placed through the left pedicle 426 a .
- the delivery tube 428 may have a inside diameter of less than about 6 mm, more narrowly from about 2 mm to about 4.5 mm.
- a bone drill can be passed through the delivery tube to form a first drill void 430 a on the left side of the vertebral body.
- a second delivery tube 428 b can be through the right pedicle 426 b .
- a second drill void 430 b can be formed on the left side of the vertebral body.
- FIG. 17B illustrates that a first balloon 20 a can be inserted into the left side of the vertebral body through the first delivery tube 428 a .
- a second balloon 20 b can be inserted into the right side of the vertebral body through the second delivery tube 428 b .
- the balloons 20 a and 20 b may be part of an inflation system 470 , such as that shown in FIG. 1 .
- FIG. 17C illustrates that fluid pressure can be delivered, as shown by arrow 438 , through the hollow shaft 2000 to the balloon 20 .
- the balloon 20 can inflate and expand, as shown by arrows 440 a and 440 b .
- the expanding balloon can compress the cancellous bone surrounding the drill void, creating a larger balloon void 442 .
- the first and second balloons can form a first void segment 454 a and a second void segment 454 b , respectively, of the balloon void 442 .
- the void segments 454 may overlap, as shown.
- the void segments 454 may be separate.
- FIG. 18 illustrates that the diametric elasticity of existing medical inflatable devices can be approximately 0.06 in/ATM and that a typical burst pressure can be about 3 ATM.
- Balloon 20 can have an exemplary diametric elasticity of 0.0004 in./ATM and a burst pressure above 20 ATM (290 psi).
- the burst pressure can be from about 290 psi to about 1500 psi. More narrowly, the burst pressure can be from about 500 psi to about 1000 psi.
- the burst pressure can be about 500 psi, about 750 psi, about 1000 psi, about 1500 psi, or higher than 1500 psi.
- the burst pressure can be greater than 4 ATM with a diameter of greater than 20 mm, with a diametric compliance of less than about 15%, or less than about 10% or less than 5%.
- FIG. 17D illustrates that the second balloon 20 b can be deflated, contracted and removed from the balloon void.
- FIG. 17E illustrates that a second cement conduit 444 b can be inserted through the second delivery tube 428 b and into the second void segment 454 b .
- Bone cement 445 can be delivered through the second cement conduit 444 b and into the second void segment 454 b .
- Cement conduits 444 a and 444 b may each be equivalent to outer assembly tube 1002 .
- FIG. 17F illustrates that the bone cement 445 can fill the second void segment 454 b and/or contact the first balloon 20 a .
- the second cement conduit 444 b can be removed from the balloon void.
- the bone cement delivered to the second void segment can cure.
- the first balloon 20 a may not erode, decay or bond to the cement.
- FIG. 17G illustrates that the first balloon 20 a can be deflated, contracted and withdrawn from the first void segment 454 a.
- FIG. 17H illustrates that a first cement conduit 444 a can be inserted through the first delivery tube 428 a and into the first void segment 454 a .
- Bone cement 445 can be delivered through the first cement conduit 444 a and into the first void segment 454 a.
- FIG. 17 i illustrates that the first and second delivery tubes 428 can be removed from the patient.
- the balloon voids 454 a and 454 b can be substantially filled with bone cement 445 .
- the bone cement 445 can cure.
- FIGS. 17 a to 17 i and FIG. 18 may also be performed with the omission of one of the two delivery tubes 428 and wherein only a single void 454 is created with one balloon 20 using access through the remaining tube 428 .
- Cement delivery device outer assembly 1000 may be filled with uncured bone cement by injecting it from, for instance, a syringe attached to bone cement filling fitting 1032 .
- Cement delivery device inner assembly 1008 may be inserted into cement device outer assembly 1000 such that advancing the inner assembly causes bone cement to be expelled at outer assembly tube end 1006 .
- the design of outer assembly tube 1002 (such as, for instance, the choice of low friction materials) may make the movement of bone cement particularly smooth and easy, regardless of the state of cure of the bone cement. For instance, advancing inner assembly handle 1012 may require from 2-8 lbs of force.
- Outer assembly tube 1002 may not bond at all to bone cement as it cures.
- Tip 1018 may fit the inside diameter of outer assembly tube 1002 such that the tip can move freely forward without allowing any bone cement to pass around the tip 1018 .
- FIGS. 19 and 20 show a method for placing material in the body, for instance for placing bone cement 445 in a vertebral body 422 .
- the bone cement 445 to be deployed from the cement delivery device 996 can be loaded into the device 996 between the distal end of the flexible portion 1016 and/or the tip 1018 and the distal port at the distal end of the device 996 .
- the cement delivery device 996 may be inserted through a cannula or delivery tube 428 .
- the distal end of the device outer assembly 1000 can exit the distal end of the delivery tube 428 into the target site of the void 442 .
- C-arm head 1080 may produce imaging x-rays for use by an operator during the procedure. Operator hands 1084 may not be in the direct x-ray path.
- the tube 1002 can be configured to have a curve, such as a 90° turn, while in the patient and/or outside the patient after the tube 1002 exits the patient.
- the tube 1002 can turn away from the C-arm head 1080 , for example enabling a user (e.g., physician) to use the device to insert the bone cement 445 into the patient without exposing, or minimizing exposure of, the energy (e.g., radiation) emitted from the head 1080 .
- a user e.g., physician
- the energy e.g., radiation
- FIG. 19 a portion of cement 445 has been placed into void 442 by translatably, slidably advancing the device inner assembly 1008 with respect to the device outer assembly 1000 .
- Tip 1018 , flexible portion 1016 and rigid portion 1020 may be visible to the operator through tube 1002 .
- Flexible portion 1016 has no significant bend in FIG. 19 .
- inner assembly 1008 has been advanced distally from the position shown in FIG. 19 .
- Flexible portion 1016 can be bent around a curve (e.g., for ergonomic improvement and/or to keep the user's hands clear of energy emitted by the C-arm head 1080 , and/or to navigate around an anatomical obstacle in vivo) in tube 1002 .
- Tip 1018 may not enter delivery tube 428 .
- the assembly may be held as shown in FIG. 20 until the bone cement cures.
- Tube end 1006 may be broken free (for instance, by twisting or bending).
- the design of tube end 1006 such as described supra, may give a very strong bond with the cone cement in tube end 1006 . This bond may make it easier to break tube end 1006 free.
- Cement delivery device 996 and delivery tube 428 may be removed.
- the internal volume of tube 1002 may contain sufficient bone cement to fill one third of the void 442 in a vertebral body, more narrowly one half of the void 442 , still more narrowly all of the cavity in a vertebral body.
- Inner assembly handle 1012 may give a precise haptic feedback to the user about pressure in the void 442 while bone cement 445 is being placed in the void 442 .
- any elements described herein as singular can be pluralized (i.e., anything described as “one” can be more than one), and plural elements can be used individually.
- Any species element of a genus element can have the characteristics or elements of any other species element of that genus.
- the term “comprising” is not meant to be limiting. The above-described configurations, elements or complete assemblies and methods and their elements for carrying out the invention, and variations of aspects of the invention can be combined and modified with each other in any combination.
Abstract
Description
- This application claims priority to U.S. Provisional Application No. 61/411,778, filed 9 Nov. 2010, which is incorporated herein by reference in its entirety.
- 1. Technical Field
- Devices and methods for a delivering a material into an orthopedic target site are disclosed. For example, devices and methods for delivering bone cement to a vertebral body are disclosed.
- 2. Description of Related Art
- It is common during orthopedic medical procedures to place materials in the bone. For instance, in vertebroplasty, bone cement is injected to stabilize a vertebral compression fracture. Similarly, in kyphoplasty, a balloon is first inserted into a vertebral body and inflated to create a void. The void is then filled with bone cement.
- Some devices for moving bone cement consist of a hand pump and a flexible tube. The tube is inserted into the orthopedic structure and bone cement is pumped through the tube and into the structure. The tube is long enough that the pump may be located up to several feet from the injection site. These devices have the advantage of allowing the physician to be removed from the injection site such that he or she is not exposed to the x-rays used to guide the filling procedure. However, tactile feedback is poor, excessive pressures can be generated and the bone cement remaining in the tube is all wasted in the end. Detaching the tube from the mass of injected bone cement can also be problematic.
- Some devices, such as those used for kyphoplasty, use a simple rigid hollow tube with a solid rigid pusher rod that slides down the tube. The hollow tube is filled with bone cement and the solid pusher rod drives the bone cement into the body. These devices have the advantage of excellent tactile feedback, simplicity, lack of waste and easy termination with the mass of injected bone cement. However, they have small volumes and, because they are used right at the injection site, may expose the physician to x-rays during the filling procedure. Finally, because of their material choices, they may require significant force to extrude cement as the cement hardens.
- What is needed is a device to place material into bone that protects physicians from X-ray exposure, has adequate volume, smooth operation, good haptics, minimizes waste and allows easy termination with the mass of injected bone cement.
- A device for delivering a material into an orthopedic target site is disclosed. The device can have a flexible tube having a first lumen having a first end and a second end. The first lumen can extend along all or part of the length of the flexible tube. The device can have a pusher having a pusher total length. The pusher can have a pusher first length along and a pusher second length. The pusher first length can abut or contact the pusher second length. The pusher first length can have a first rigidity. The pusher second length can have a second rigidity. The first rigidity can be less than or greater than the second rigidity. The pusher and tube can be configured for the pusher to be slidably received by a port at the proximal end of the first lumen. The material to be delivered can be located in the first lumen between the pusher and the distal end of the flexible tube.
- The pusher first length can be at least about 10% of the pusher total length. The pusher second length can be at least about 10% of the pusher total length.
- The material can be or have a bone cement. The flexible tube can have a low friction material configured to resist binding to the bone cement.
- The flexible tube can be translucent and/or transparent. The flexible tube can have a second lumen along all or part of the length of the flexible tube. The pusher second length can have a cable.
- A method for delivering a material into an orthopedic target site is disclosed. The method can include slidably positioning a pusher into a first lumen of a flexible tube. The first lumen can have a first port and a second port. The pusher can have a pusher first length and a pusher second length. The pusher first length can be more rigid or less rigid than the pusher second length. The method can include loading the first lumen with the material between the pusher second length and the second port. The method can include positioning the flexible tube so the flexible tube is configured to have at least a first curve, for example to navigate around an anatomical obstruction. Positioning the flexible tube can include the second port being located at the orthopedic target site. The method can include moving the pusher from a first pusher position to a second pusher position. Moving the pusher from the first pusher position to the second pusher position can include moving the pusher second length across the first curve. The method can include deploying the material from the lumen to the orthopedic target site.
- The deploying of the material is concurrent with the moving of the pusher from the first pusher position to the second pusher position. The material to be delivered to the orthopedic target site can be or have a bone cement.
- The method can include stopping a flow of the material. The stopping of the flow can include ceasing a translational movement of the pusher with respect to the flexible tube.
- The method can include removing the flexible tube from the orthopedic target site. The method can include creating a void at the orthopedic target site.
- The method can include positioning a cannula at the orthopedic target site. The cannula can have a cannula distal port open to the orthopedic target site once the cannula is positioned. Positioning the flexible tube can include moving the flexible tube through the cannula, for example, until the distal port of the flexible tube exits the cannula distal port.
- A method for delivering a material into an orthopedic target site is disclosed. The method can include positioning a device at the orthopedic target site. The pusher or advancement rod can have an advancement rod first length and an advancement rod second length. The advancement rod first length can have a different rigidity than a rigidity of the advancement rod second length. The method can include advancing the advancement rod from an advancement rod proximal position to an advancement rod distal position. During the advancing of the advancement rod, the first length of the advancement rod can be non-collinear with the advancement rod second length. The method can include deploying the material from the device to the orthopedic target site.
- The material can be deployed preceding, subsequent to, concurrent with, or combinations thereof, the advancing of the advancement rod.
-
FIG. 1 illustrates a variation of a void creation tool. -
FIG. 2 a illustrates a variation of the material delivery device. -
FIGS. 2 b and 2 c are cross-sections B-B and C-C, respectively, of a variation of the device. -
FIGS. 2 d and 2 e are cross-sections B-B and C-C, respectively, of a variation of the device. -
FIG. 3 illustrates a variation of the device dissembled. -
FIG. 4 illustrates a variation of the delivery device inner assembly in a curved configuration. -
FIG. 5 illustrates a variation of the delivery device outer assembly in a curved configuration. -
FIG. 6 is a close-up cross-section of a length of the device. -
FIG. 7 is a close-up view of a length of a variation of the device. -
FIG. 8 is a close-up view of a length of a variation of the proximal end of the device. -
FIG. 9 is a close-up view of a length of a variation of the distal end of the device. -
FIGS. 10A through 10E illustrate variations of cross-section A-A. -
FIGS. 11 a and 11 b are close-up, phantom views of variations of the distal end of the device. -
FIGS. 12 a and 12 b illustrate a variation of a method for controllably closing the distal end of the device. -
FIGS. 13 a and 13 b illustrate a variation of a method for controllably closing the distal end of the device. -
FIGS. 14 a and 14 c illustrate a variation of a method for controllably opening and closing the distal end of the device. -
FIG. 15 is a sagittal section of a patient including a full view of a spine. -
FIG. 16 is a close-up transverse section of a patient including a vertebra and the adjacent nerves including the spinal cord. -
FIGS. 17A through 17 i illustrate a method for creating one or more voids at a target site within a vertebral body, filling the voids with a filler material such as bone cement, and withdrawing surgical tools for creating the voids and delivering the filler material from the target site. -
FIG. 18 is a graph showing pressure verse diameter for variations of balloons including burst pressures. -
FIGS. 19 and 20 illustrate methods for using the delivery device. -
FIG. 1 illustrates that aninflation system 470 can have an expandable void-creation volume such asballoon 20 that can be inflated by pushing inflation fluid, such as water, saline, a gel or dye, from thesyringe 472, into theinflation port 482, through thehollow shaft lumen 154 and into theballoon 20. Thesyringe 472 can be detachable or non-detachable from the remainder of theinflation system 470. - The stiffening
rod 474 can be removed from theinflation system 470 or left in place to stiffen theinflation system 470 while positioning theballoon 20 in the body. The stiffeningrod tip 484 can have atraumatic geometry, or a soft plastic or elastomeric tip that will minimize puncture or damage the distal end of the balloon. Theinflation system 470 can have astiffening rod control 480, for example a knob or handle on the proximal end of theinflation system 470 to control the position of the stiffeningrod 474. Aseal 286 adjacent to the stiffening rod control can prevent pressure from escaping from the hollow shaft lumen. When theballoon 20 is at the target site, the stiffeningrod 474 can be removed from the inflation system or left in place. -
FIG. 2 a illustrates a delivery service or system that may be used to deliver a material, such as one or more bone cements, morselized bone, or combinations thereof, into the body.Cement delivery device 996 may be comprised of cement delivery deviceouter assembly 1000 and cement delivery deviceinner assembly 1008.Inner assembly 1008 may be inserted intoouter assembly 1000 such that theinner assembly 1008 can slide relative to theouter assembly 1000. -
FIG. 3 shows that the cement delivery deviceouter assembly 1000 may compriseouter assembly tube 1002,outer assembly handle 1004, outerassembly tube end 1006 with an outer assemblytube end length 1007 and bonecement filling fitting 1032.Outer assembly tube 1002 may be comprised of a low-friction material such as PTFE, LDPE or the like. For instance,tube 1002 may be made of a material that has a dynamic coefficient of friction with steel of less than 0.3, more narrowly less than 0.2, still more narrowly less than 0.1. The low-friction material can resist binding to the bone cement. -
Outer assembly tube 1002 may be flexible, rigid, semi-flexible, or combinations thereof, for example alternating along the length of theouter assembly tube 1002.Outer assembly tube 1002 may be opaque, clear, transparent, translucent or combinations thereof.Outer assembly tube 1002 may comprise a fiber reinforcement element, such as a braid. This fiber reinforcement element may increase radial stiffness when thetube 1002 is pressurized.Outer assembly tube 1002 may have an outer diameter of less than about 0.32 inches (8.1 mm), more narrowly less than 0.2 inches (5 mm).Outer assembly tube 1002 may have a length of 12-32 inches (304-813 mm).Outer assembly tube 1002 may have about a 0.138 inch (3.50 mm) outer diameter and about a 0.108 inch (2.74 mm) inner diameter and about a length of 20 inches (508 mm). -
FIG. 3 shows that the cement delivery deviceinner assembly 1008 may comprise an innerassembly pushing device 1014 and aninner assembly handle 1012. Pusher, advancement rod, or innerassembly pushing device 1014 may comprise a pushing devicerigid portion 1020 with a pushing devicerigid portion length 1028, and a pushing deviceflexible portion 1016 with a pushing deviceflexible portion length 1024 and a pushing deviceflexible portion tip 1018. - The pushing device
rigid portion length 1028 can be about 10% or more, or yet more narrowly greater than or equal to about 25%, for example about 65% of the entire length of the innerassembly pushing device 1014. The pushing deviceflexible portion length 1024 can be about 10% or more, or, yet more narrowly greater than or equal to about 25%, or for example about 35% of the entire length of the innerassembly pushing device 1014. The pushing devicerigid portion length 1028 and the pushing deviceflexible portion length 1024 can combine to be about the entire length of the innerassembly pushing device 1014. - The pushing device
rigid portion 1020 can abut, be integral with, or contact the pushing deviceflexible portion 1016. For example, the pushing deviceflexible portion 1016 can be a cable fused, hound, clipped, wedged into a port in the distal end of the pushing devicerigid portion 1020, or combinations thereof. - The pushing device
rigid portion 1020 may be a rod or a tube or a semi-rigid cable with an outside diameter of about 0.050-0.090 inches (1.27-2.29 mm). The pushing devicerigid portion length 1028 may be about 7-15 inches (178-381 mm). The pushing deviceflexible portion 1016 may be a semi-rigid cable or semi-flexible cable with a diameter of about, 0.040-0.080 inches (1.02-2.03 mm), more narrowly 1/16 of an inch (1.59 mm). The pushing deviceflexible portion 1016 may be attached to the pushing devicerigid portion 1020 by a bond, a crimp, a weld, a braze or some combination thereof. The pushing deviceflexible portion length 1024 may be about 1-7 inches (25-178 mm). The pushing deviceflexible portion tip 1018 may be comprised of an additional short section of tubing, a tightly bonded termination of the cable, a crimp fitting, or combinations thereof. The pushing deviceflexible portion 1016 may be omitted entirely from the innerassembly pushing device 1014. -
FIGS. 2 b and 2 c illustrate a variation of cross-sections B-B and C-C respectively.FIG. 2 b illustrates that thetube 1002 can have alumen 1100. Thetube 1002 can have multiple, separated lumens. Thelumen 1100 can extend all or a part of the length of thetube 1002. Along the pushing devicerigid portion length 1028 the pushing devicerigid portion 1020 of theinner assembly 1008 can have a uniform solid or hollow circular cross-section.FIG. 2 c illustrates that along the pushing deviceflexible portion length 1024, the pushing deviceflexible portion 1016 of theinner assembly 1008 can be porous, woven and/or braided, for example, as a cable. - The diameter of the pushing device
rigid portion 1020 can be greater than, equal to, or less than the diameter of the pushing deviceflexible portion 1016. The gap between the radially inner surface of thetube 1002 and the radially outer surface of the pushing devicerigid portion 1020 and/or the pushing deviceflexible portion 1016 can be nominal (e.g., sufficient to allow sliding), or large enough to allow deployment delivery of bone cement or other materials through the gap. -
FIGS. 2 d and 2 e illustrate a variation of cross-sections B-B and C-C respectively.FIG. 2 d illustrates that along the pushing devicerigid portion length 1028 the pushing devicerigid portion 1020 of theinner assembly 1008 can have a circular cross-section orcylindrical core 1102. Thecore 1102 can be radially surrounded by a solid or cabled stiffening sheath 1104. Thecore 1102 can have a smaller radius than the stiffening sheath 1104. The core can be made from thesame material 1102 or a different material than the sheath 1104.FIG. 2 e illustrates that along the pushing deviceflexible portion length 1024, the pushing deviceflexible portion 1016 of theinner assembly 1008 can have thecore 1102, for example unsurrounded by the stiffening sheath 1104. -
FIG. 4 shows thatflexible portion 1016 may be bent to form anangle 1092 by applying aforce 1088 normal to the longitudinal axis offlexible portion 1016 using, for instance,operator hand 1084.Angle 1092 may be greater than about 45 degrees, more narrowly greater than about 90 degrees.Force 1088 may be less than 30 newtons, more narrowly less than 15 newtons, more narrowly less than 5 newtons, still more narrowly less than 2.5 newtons For instance, pushing device flexible portion length may 1024 may be about 3 inches long,force 1088 may be about 1 newton andangle 1092 may be about 90 degrees. Applying and then removingforce 1088 toflexible portion 1016 may not result in any significant permanent deformation in the shape offlexible portion 1016. - The
flexible portion 1016 can be straight and/or bend having a radius of curvature of greater than or equal to about 4 in., more narrowly about 3 in, yet more narrowly about 1 in. Thetube 1002, for example along the length at which theflexible portion 1016 is positioned, can curve to a radius of curvature about equal to the radius of curvature of about the radius of curvature of theflexible portion 1016, e.g., being straight, having a radius of curvature of greater than or equal to about 4 in., more narrowly about 3 in, yet more narrowly about 1 in. -
FIG. 5 shows thatouter assembly 1000 can be flexible. For instance,tube 1002 can be deformed into a circle without any significant permanent deformation. -
FIG. 6 shows the pushing deviceflexible portion 1016 and the pushing deviseflexible portion tip 1018 sliding withinouter assembly tube 1002. As shown, pushing deviceflexible portion 1016 and the pushing deviceflexible portion tip 1018 may be visible through the walls ofouter assembly tube 1002. -
FIG. 7 shows thatouter assembly tube 1002 may be made in a curved or spiral shape.Outer assembly tube 1002 may comprise atube reinforcement spring 1036 wrapped around the outside diameter of the tube.Spring 1036 may maketube 1002 stiffer and/or give tube 1002 a higher burst pressure. -
FIG. 8 showsouter assembly handle 1004 and bone cement filling fitting 1032 attached toouter assembly tube 1002. Bone cement filling fitting 1032 may be, for instance, a luer fitting. -
FIG. 9 shows a possible configuration of the outerassembly tube end 1006.Tube end 1006 may be a fitting with a smaller inside diameter thanouter assembly tube 1002.Tube end 1006 can be a straight rigid tube. Outerassembly tube end 1006 may be made of a material that bonds well to bone cement. For instance, it could be made of a metal, or a porous material that bone cement may flow into. -
FIGS. 10A-E show variations of cross-section A-A of outerassembly tube end 1006.Tube end 1006 can have one ormore vanes 1040 that extend over all or part of thelength 1007 oftube end 1006. The vanes can furcate (e.g., bifurcate, trifurcate, quadfurcate) thetube end 1006 orentire tube 1008 into multiple lumens.Vanes 1040 maybe made of a material that forms a strong bond with bone cement.Vanes 1040 may increase the area available for bone cement to bond intube end 1006, thus increasing bond strength.Tube end 1006 may be solid except forholes 1042 that pass lengthwise throughend 1006. For instance,tube end 1006 may have 1, 2, 3, 4, 5, more than 5, more than 10 or more than 50lengthwise holes 1042. Eachhole 1042 can be in fluid communication with a single lumen in the tube or eachhole 1042 can be in communication with separate lumens in the tube. -
FIGS. 11 a and 11 b showtube 1002 withtube end 1006.Tube end 1006 is, for instance, a plug which half covers the exits oftube 1002.Inner tube 1076 is sized to pass thru the inner diameter oftube 1002 and has and end plug which covers about half the exit ofinner tube 1076. In one rotational orientation ofinner tube 1076, shown inFIG. 11 a, material may exittube 1002 attube end 1006. In a second rotational orientation ofinner tube 1076, shown inFIG. 11 b, material is blocked from exitingtube 1002. By rotatinginner tube 1076 withintube end 1006, the distal end oftube 1002 may be closed. This closing may serve to severtube end 1006 from the material immediately distal totube end 1006. -
FIGS. 12 a-12 b shows amaterial flow valve 1048. Thevalve 1048 may consist of a circular flapper mounted on a pivot. InFIG. 12 a, the flapper is turned vertically allowing material to flow. InFIG. 12 b, the flapper is turned horizontally, stopping the flow of material. -
FIGS. 13 a-13 b show thatouter assembly tube 1002 can be circumferentially closed by pullingcable 1044. -
FIGS. 14 a-14 c show a material flow valve that is activated passively. InFIG. 14 a,bone cement 445 is flowing towardscement flow valve 1048. InFIG. 14 b, thebone cement 445 has reachedcement flow valve 1048 and the back pressure on thebone cement 445 has causedcement flow valve 1048 to open. InFIG. 14 c, the back pressure on thebone cement 445 is now not sufficient to holdcement flow valve 1048 open and it closes automatically. -
FIG. 15 illustrates a sagittal view of a patient and thespine 406. Thespine 406 can havevertebrae 408 and cervical, thoracic, lumbar andsacral regions device vertebrae 408 in any region of thespine 406. -
FIG. 16 illustrates avertebrae 408 that can havecortical bone 418 andcancellous bone 420. Thevertebrae 408 can have a vertebral body 422 avertebral process 424 andpedicles 426. -
FIGS. 17A through 17 i illustrate a method for deployingballoons 20 bilaterally, for example including one balloon inserted through each of opposingpedicles -
FIG. 17A illustrates that afirst delivery tube 428 a, such as a cannula, can be placed through theleft pedicle 426 a. Thedelivery tube 428 may have a inside diameter of less than about 6 mm, more narrowly from about 2 mm to about 4.5 mm. A bone drill can be passed through the delivery tube to form afirst drill void 430 a on the left side of the vertebral body. Asecond delivery tube 428 b can be through theright pedicle 426 b. Asecond drill void 430 b can be formed on the left side of the vertebral body. -
FIG. 17B illustrates that afirst balloon 20 a can be inserted into the left side of the vertebral body through thefirst delivery tube 428 a. Asecond balloon 20 b can be inserted into the right side of the vertebral body through thesecond delivery tube 428 b. Theballoons inflation system 470, such as that shown inFIG. 1 . -
FIG. 17C illustrates that fluid pressure can be delivered, as shown by arrow 438, through thehollow shaft 2000 to theballoon 20. Theballoon 20 can inflate and expand, as shown byarrows larger balloon void 442. The first and second balloons can form afirst void segment 454 a and a second void segment 454 b, respectively, of theballoon void 442. The void segments 454 may overlap, as shown. The void segments 454 may be separate. -
FIG. 18 illustrates that the diametric elasticity of existing medical inflatable devices can be approximately 0.06 in/ATM and that a typical burst pressure can be about 3 ATM.Balloon 20 can have an exemplary diametric elasticity of 0.0004 in./ATM and a burst pressure above 20 ATM (290 psi). For example, the burst pressure can be from about 290 psi to about 1500 psi. More narrowly, the burst pressure can be from about 500 psi to about 1000 psi. For example, the burst pressure can be about 500 psi, about 750 psi, about 1000 psi, about 1500 psi, or higher than 1500 psi. For example, the burst pressure can be greater than 4 ATM with a diameter of greater than 20 mm, with a diametric compliance of less than about 15%, or less than about 10% or less than 5%. -
FIG. 17D illustrates that thesecond balloon 20 b can be deflated, contracted and removed from the balloon void. -
FIG. 17E illustrates that a second cement conduit 444 b can be inserted through thesecond delivery tube 428 b and into the second void segment 454 b.Bone cement 445 can be delivered through the second cement conduit 444 b and into the second void segment 454 b. Cement conduits 444 a and 444 b may each be equivalent toouter assembly tube 1002. -
FIG. 17F illustrates that thebone cement 445 can fill the second void segment 454 b and/or contact thefirst balloon 20 a. The second cement conduit 444 b can be removed from the balloon void. The bone cement delivered to the second void segment can cure. Thefirst balloon 20 a may not erode, decay or bond to the cement. -
FIG. 17G illustrates that thefirst balloon 20 a can be deflated, contracted and withdrawn from thefirst void segment 454 a. -
FIG. 17H illustrates that a first cement conduit 444 a can be inserted through thefirst delivery tube 428 a and into thefirst void segment 454 a.Bone cement 445 can be delivered through the first cement conduit 444 a and into thefirst void segment 454 a. -
FIG. 17 i illustrates that the first andsecond delivery tubes 428 can be removed from the patient. The balloon voids 454 a and 454 b can be substantially filled withbone cement 445. Thebone cement 445 can cure. - The procedure described in
FIGS. 17 a to 17 i andFIG. 18 may also be performed with the omission of one of the twodelivery tubes 428 and wherein only a single void 454 is created with oneballoon 20 using access through the remainingtube 428. - Cement delivery device
outer assembly 1000 may be filled with uncured bone cement by injecting it from, for instance, a syringe attached to bonecement filling fitting 1032. Cement delivery deviceinner assembly 1008 may be inserted into cement deviceouter assembly 1000 such that advancing the inner assembly causes bone cement to be expelled at outerassembly tube end 1006. The design of outer assembly tube 1002 (such as, for instance, the choice of low friction materials) may make the movement of bone cement particularly smooth and easy, regardless of the state of cure of the bone cement. For instance, advancinginner assembly handle 1012 may require from 2-8 lbs of force.Outer assembly tube 1002 may not bond at all to bone cement as it cures.Tip 1018 may fit the inside diameter ofouter assembly tube 1002 such that the tip can move freely forward without allowing any bone cement to pass around thetip 1018. -
FIGS. 19 and 20 show a method for placing material in the body, for instance for placingbone cement 445 in avertebral body 422. Thebone cement 445 to be deployed from thecement delivery device 996 can be loaded into thedevice 996 between the distal end of theflexible portion 1016 and/or thetip 1018 and the distal port at the distal end of thedevice 996. - As shown in
FIGS. 19 and 20 , thecement delivery device 996 may be inserted through a cannula ordelivery tube 428. The distal end of the deviceouter assembly 1000 can exit the distal end of thedelivery tube 428 into the target site of thevoid 442. C-arm head 1080 may produce imaging x-rays for use by an operator during the procedure.Operator hands 1084 may not be in the direct x-ray path. Thetube 1002 can be configured to have a curve, such as a 90° turn, while in the patient and/or outside the patient after thetube 1002 exits the patient. Thetube 1002 can turn away from the C-arm head 1080, for example enabling a user (e.g., physician) to use the device to insert thebone cement 445 into the patient without exposing, or minimizing exposure of, the energy (e.g., radiation) emitted from thehead 1080. - In
FIG. 19 , a portion ofcement 445 has been placed intovoid 442 by translatably, slidably advancing the deviceinner assembly 1008 with respect to the deviceouter assembly 1000.Tip 1018,flexible portion 1016 andrigid portion 1020 may be visible to the operator throughtube 1002.Flexible portion 1016 has no significant bend inFIG. 19 . - In
FIG. 20 ,inner assembly 1008 has been advanced distally from the position shown inFIG. 19 .Flexible portion 1016 can be bent around a curve (e.g., for ergonomic improvement and/or to keep the user's hands clear of energy emitted by the C-arm head 1080, and/or to navigate around an anatomical obstacle in vivo) intube 1002.Tip 1018 may not enterdelivery tube 428. The assembly may be held as shown inFIG. 20 until the bone cement cures.Tube end 1006 may be broken free (for instance, by twisting or bending). The design oftube end 1006, such as described supra, may give a very strong bond with the cone cement intube end 1006. This bond may make it easier to breaktube end 1006 free.Cement delivery device 996 anddelivery tube 428 may be removed. - The internal volume of
tube 1002 may contain sufficient bone cement to fill one third of the void 442 in a vertebral body, more narrowly one half of the void 442, still more narrowly all of the cavity in a vertebral body.Inner assembly handle 1012 may give a precise haptic feedback to the user about pressure in the void 442 whilebone cement 445 is being placed in thevoid 442. - U.S. patent application Ser. Nos. 12/537,166, filed 6 Aug. 2009; and 12/477,057, filed 2 Jun. 2009 are incorporated by reference herein in their entireties.
- Any elements described herein as singular can be pluralized (i.e., anything described as “one” can be more than one), and plural elements can be used individually. Any species element of a genus element can have the characteristics or elements of any other species element of that genus. The term “comprising” is not meant to be limiting. The above-described configurations, elements or complete assemblies and methods and their elements for carrying out the invention, and variations of aspects of the invention can be combined and modified with each other in any combination.
Claims (20)
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
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US13/293,058 US10188436B2 (en) | 2010-11-09 | 2011-11-09 | Inflatable medical devices |
US16/241,220 US10966763B2 (en) | 2010-11-09 | 2019-01-07 | Inflatable medical devices |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US41177810P | 2010-11-09 | 2010-11-09 | |
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Cited By (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20110060186A1 (en) * | 2008-04-27 | 2011-03-10 | Alexander Quillin Tilson | Biological navigation device |
US8708955B2 (en) | 2008-06-02 | 2014-04-29 | Loma Vista Medical, Inc. | Inflatable medical devices |
CN103908332A (en) * | 2013-01-09 | 2014-07-09 | 上海凯利泰医疗科技股份有限公司 | Equipment for injecting bone cement |
US9592119B2 (en) | 2010-07-13 | 2017-03-14 | C.R. Bard, Inc. | Inflatable medical devices |
US9730707B2 (en) | 2014-08-20 | 2017-08-15 | Kyphon SÀRL | Surgical instrument with graduated markings correlating to angulation |
US20190008566A1 (en) * | 2001-11-03 | 2019-01-10 | DePuy Synthes Products, Inc. | Device for straightening and stabilizing the vertebral column |
US10188273B2 (en) | 2007-01-30 | 2019-01-29 | Loma Vista Medical, Inc. | Biological navigation device |
CN113827352A (en) * | 2021-09-17 | 2021-12-24 | 海南医学院 | Dental pile drives with oral cavity prosthetic devices |
Citations (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US833044A (en) * | 1906-03-13 | 1906-10-09 | Claudius Ash Sons & Company 1905 Ltd | Dental instrument. |
US1469004A (en) * | 1920-03-05 | 1923-09-25 | Holtz Gustav | Amalgam carrier and plugger |
US3724076A (en) * | 1971-04-05 | 1973-04-03 | Vac O Cast | Dental cement gun |
US4215985A (en) * | 1977-09-13 | 1980-08-05 | Establissement Dentaire Ivoclar | Mixing container |
US4431414A (en) * | 1982-01-25 | 1984-02-14 | Lawrence John S | Dental syringe for filling cavities in teeth |
US4757827A (en) * | 1987-02-17 | 1988-07-19 | Versaflex Delivery Systems Inc. | Steerable guidewire with deflectable tip |
US4769011A (en) * | 1985-03-28 | 1988-09-06 | Interpore International, Inc. | Syringe apparatus and method for the surgical implantation of granular substances |
US5637092A (en) * | 1995-01-30 | 1997-06-10 | Shaw; Thomas J. | Syringe plunger locking assembly |
US5849014A (en) * | 1997-03-20 | 1998-12-15 | Johnson & Johnson Professional, Inc. | Cement restrictor system and method of forming a cement plug within the medullary canal of a bone |
US6348055B1 (en) * | 1999-03-24 | 2002-02-19 | Parallax Medical, Inc. | Non-compliant system for delivery of implant material |
US6730095B2 (en) * | 2002-06-26 | 2004-05-04 | Scimed Life Systems, Inc. | Retrograde plunger delivery system |
US20050070915A1 (en) * | 2003-09-26 | 2005-03-31 | Depuy Spine, Inc. | Device for delivering viscous material |
US20060259006A1 (en) * | 2005-04-29 | 2006-11-16 | Mckay William F | Devices and methods for delivering medical agents |
US20070162042A1 (en) * | 2003-11-18 | 2007-07-12 | Thomas Dunker | Injection pump |
US20070233146A1 (en) * | 2006-01-27 | 2007-10-04 | Stryker Corporation | Low pressure delivery system and method for delivering a solid and liquid mixture into a target site for medical treatment |
US7513901B2 (en) * | 2005-05-19 | 2009-04-07 | Warsaw Orthopedic, Inc. | Graft syringe assembly |
US20100056989A1 (en) * | 2005-04-29 | 2010-03-04 | Warsaw Orthopedic, Inc. | Instrumentation for injection of therapeutic fluid into joints |
US20110034885A1 (en) * | 2009-08-05 | 2011-02-10 | The University Of Toledo | Needle for directional control of the injection of bone cement into a vertebral compression fracture |
US8062254B2 (en) * | 2008-01-08 | 2011-11-22 | MacLean, LLC | Spring driven adjustable oral syringe |
Family Cites Families (356)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3533578A (en) | 1967-08-22 | 1970-10-13 | Ed Lesh | Lighter than air craft non-rigid pressure ships and tethered glider or plane,heavier than air |
US3924632A (en) | 1972-12-07 | 1975-12-09 | William A Cook | Fiber glass reinforced catheter |
JPS5239596B2 (en) | 1974-04-04 | 1977-10-06 | ||
US3970495A (en) | 1974-07-24 | 1976-07-20 | Fiber Science, Inc. | Method of making a tubular shaft of helically wound filaments |
AT348094B (en) | 1977-02-17 | 1979-01-25 | Hanecka Lubomir Dipl Ing | BALLOON CATHETER |
US4176662A (en) | 1977-06-17 | 1979-12-04 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Apparatus for endoscopic examination |
US4321915A (en) | 1979-06-26 | 1982-03-30 | The United States Of America As Represented By The Department Of Health And Human Services | Everting tube device with relative advance control |
US4327736A (en) | 1979-11-20 | 1982-05-04 | Kanji Inoue | Balloon catheter |
US4563171A (en) | 1980-03-28 | 1986-01-07 | Sherwood Medical Company | Method for displacing fluid in tubing |
US4553959A (en) | 1982-01-27 | 1985-11-19 | The Victoria University Of Manchester | Urethral catheter |
US4516972A (en) | 1982-01-28 | 1985-05-14 | Advanced Cardiovascular Systems, Inc. | Guiding catheter and method of manufacture |
US4525228A (en) | 1982-08-13 | 1985-06-25 | United Kingdom Atomic Energy Authority | Method of winding on foam mandrel |
SE462949B (en) | 1982-10-14 | 1990-09-24 | Eschmann Bros & Walsh Ltd | dilatation catheter |
US4517979A (en) | 1983-07-14 | 1985-05-21 | Cordis Corporation | Detachable balloon catheter |
US4702252A (en) | 1983-10-13 | 1987-10-27 | Smiths Industries Public Limited Company | Catheters |
US4637396A (en) | 1984-10-26 | 1987-01-20 | Cook, Incorporated | Balloon catheter |
US4690131A (en) | 1985-05-31 | 1987-09-01 | The United States Of America As Represented By The Department Of Health And Human Services | Medical apparatus |
DE3675652D1 (en) | 1985-07-19 | 1990-12-20 | Meadox Medicals Inc | EXPANSION CATHETER OR BALLOON CATHETER. |
US4706670A (en) | 1985-11-26 | 1987-11-17 | Meadox Surgimed A/S | Dilatation catheter |
US4863440A (en) | 1985-12-23 | 1989-09-05 | Thomas J. Fogarty | Pressurized manual advancement dilatation catheter |
JPH025799Y2 (en) | 1986-02-07 | 1990-02-13 | ||
US4779611A (en) | 1987-02-24 | 1988-10-25 | Grooters Ronald K | Disposable surgical scope guide |
US4894281A (en) | 1987-05-29 | 1990-01-16 | Mitsui Petrochemical Industries, Ltd. | Fiber-reinforced polymer molded body |
US4809678A (en) | 1987-08-14 | 1989-03-07 | Klein Richard S | Endoscope for preventing patient contamination |
US4881553A (en) | 1987-11-20 | 1989-11-21 | Grossman Richard A | Mesh reinforced condom |
NO890322L (en) | 1988-02-28 | 1989-08-29 | Inst Textil Und Faserforsch St | Catheter. |
US4852551A (en) | 1988-04-22 | 1989-08-01 | Opielab, Inc. | Contamination-free endoscope valves for use with a disposable endoscope sheath |
US4952357A (en) | 1988-08-08 | 1990-08-28 | Scimed Life Systems, Inc. | Method of making a polyimide balloon catheter |
US5192296A (en) | 1988-08-31 | 1993-03-09 | Meadox Medicals, Inc. | Dilatation catheter |
US5462705A (en) | 1988-10-27 | 1995-10-31 | Labsphere, Inc. | Method of forming diffusely reflecting sintered fluorinated long-chain addition polymers doped with pigments for color standard use |
US5236423A (en) | 1988-12-13 | 1993-08-17 | Endomed Corporation | Facilitating endoscopy |
US5087246A (en) | 1988-12-29 | 1992-02-11 | C. R. Bard, Inc. | Dilation catheter with fluted balloon |
GB8900263D0 (en) | 1989-01-06 | 1989-03-08 | Pearpoint Ltd | Miniature tv camera systems |
CA1329091C (en) | 1989-01-31 | 1994-05-03 | Geoffrey S. Martin | Catheter with balloon retainer |
US4969888A (en) | 1989-02-09 | 1990-11-13 | Arie Scholten | Surgical protocol for fixation of osteoporotic bone using inflatable device |
US5137512A (en) | 1989-03-17 | 1992-08-11 | Scimed Life Systems, Inc. | Multisegment balloon protector for dilatation catheter |
US5112304A (en) | 1989-03-17 | 1992-05-12 | Angeion Corporation | Balloon catheter |
US5147302A (en) | 1989-04-21 | 1992-09-15 | Scimed Life Systems, Inc. | Method of shaping a balloon of a balloon catheter |
JP2545981B2 (en) | 1989-05-09 | 1996-10-23 | 東レ株式会社 | Balloon catheter |
US5116318A (en) | 1989-06-06 | 1992-05-26 | Cordis Corporation | Dilatation balloon within an elastic sleeve |
DE3943872B4 (en) | 1989-08-01 | 2005-08-25 | Stm Medizintechnik Starnberg Gmbh | Device for introducing a medical endoscope into a body canal |
US5318587A (en) | 1989-08-25 | 1994-06-07 | C. R. Bard, Inc. | Pleated balloon dilatation catheter and method of use |
DE69002295T2 (en) | 1989-09-25 | 1993-11-04 | Schneider Usa Inc | MULTILAYER EXTRUSION AS A METHOD FOR PRODUCING BALLOONS FOR VESSEL PLASTICS. |
US5108370A (en) | 1989-10-03 | 1992-04-28 | Paul Walinsky | Perfusion balloon catheter |
US5217440A (en) | 1989-10-06 | 1993-06-08 | C. R. Bard, Inc. | Multilaminate coiled film catheter construction |
US5290306A (en) | 1989-11-29 | 1994-03-01 | Cordis Corporation | Puncture resistant balloon catheter |
US6626888B1 (en) | 1990-01-10 | 2003-09-30 | Rochester Medical Corporation | Method of shaping structures with an overcoat layer including female urinary catheter |
US5163949A (en) | 1990-03-02 | 1992-11-17 | Bonutti Peter M | Fluid operated retractors |
US5342301A (en) | 1992-08-13 | 1994-08-30 | Advanced Polymers Incorporated | Multi-lumen balloons and catheters made therewith |
US5181911A (en) | 1991-04-22 | 1993-01-26 | Shturman Technologies, Inc. | Helical balloon perfusion angioplasty catheter |
US5190058A (en) | 1991-05-22 | 1993-03-02 | Medtronic, Inc. | Method of using a temporary stent catheter |
US5250070A (en) | 1991-05-28 | 1993-10-05 | Parodi Juan C | Less traumatic angioplasty balloon for arterial dilatation |
CA2074304C (en) | 1991-08-02 | 1996-11-26 | Cyril J. Schweich, Jr. | Drug delivery catheter |
JPH05192408A (en) | 1991-09-06 | 1993-08-03 | C R Bard Inc | Production of expansion balloon |
JPH05184526A (en) | 1991-09-17 | 1993-07-27 | Olympus Optical Co Ltd | Bending mechanism for flexible tube |
US5226888A (en) | 1991-10-25 | 1993-07-13 | Michelle Arney | Coiled, perfusion balloon catheter |
US5395349A (en) | 1991-12-13 | 1995-03-07 | Endovascular Technologies, Inc. | Dual valve reinforced sheath and method |
FR2686256A1 (en) | 1992-01-17 | 1993-07-23 | Nycomed Ingenor Sa Lab | Dilation catheter |
US5295959A (en) | 1992-03-13 | 1994-03-22 | Medtronic, Inc. | Autoperfusion dilatation catheter having a bonded channel |
US5325846A (en) | 1992-07-27 | 1994-07-05 | Linvatec Corporation | Endoscopic draping apparatus and method |
US6623516B2 (en) | 1992-08-13 | 2003-09-23 | Mark A. Saab | Method for changing the temperature of a selected body region |
US5295995A (en) | 1992-08-27 | 1994-03-22 | Kleiman Jay H | Perfusion dilatation catheter |
US5662587A (en) | 1992-09-16 | 1997-09-02 | Cedars Sinai Medical Center | Robotic endoscopy |
US5333568A (en) | 1992-11-17 | 1994-08-02 | America3 Foundation | Material for the fabrication of sails |
US5383467A (en) | 1992-11-18 | 1995-01-24 | Spectrascience, Inc. | Guidewire catheter and apparatus for diagnostic imaging |
DE4244990C2 (en) | 1992-12-15 | 2002-03-14 | Stm Medtech Starnberg | Device for moving an endoscope shaft along a channel-like cavity |
CA2114988A1 (en) | 1993-02-05 | 1994-08-06 | Matthew O'boyle | Ultrasonic angioplasty balloon catheter |
US5403280A (en) | 1993-02-16 | 1995-04-04 | Wang; James C. | Inflatable perfusion catheter |
US5308356A (en) | 1993-02-25 | 1994-05-03 | Blackshear Jr Perry L | Passive perfusion angioplasty catheter |
US5645529A (en) | 1993-03-11 | 1997-07-08 | C. R. Bard, Inc. | Devices for selectively directing inflation devices |
US5383856A (en) | 1993-03-19 | 1995-01-24 | Bersin; Robert M. | Helical spiral balloon catheter |
JPH07934A (en) | 1993-06-18 | 1995-01-06 | Mitsubishi Chem Corp | Washing method and washing device for winding core for sheet |
US5527325A (en) | 1993-07-09 | 1996-06-18 | Device For Vascular Intervention, Inc. | Atherectomy catheter and method |
US5388590A (en) | 1993-07-28 | 1995-02-14 | Medtronic, Inc. | Catheter exchange device |
CA2125258C (en) | 1993-08-05 | 1998-12-22 | Dinah B Quiachon | Multicapsule intraluminal grafting system and method |
US6025044A (en) | 1993-08-18 | 2000-02-15 | W. L. Gore & Associates, Inc. | Thin-wall polytetrafluoroethylene tube |
US5409495A (en) | 1993-08-24 | 1995-04-25 | Advanced Cardiovascular Systems, Inc. | Apparatus for uniformly implanting a stent |
US5398670A (en) | 1993-08-31 | 1995-03-21 | Ethicon, Inc. | Lumen traversing device |
US5496276A (en) | 1993-09-20 | 1996-03-05 | Scimed Life Systems, Inc. | Catheter balloon with retraction coating |
US5545209A (en) | 1993-09-30 | 1996-08-13 | Texas Petrodet, Inc. | Controlled deployment of a medical device |
WO1995009667A1 (en) | 1993-10-01 | 1995-04-13 | Boston Scientific Corporation | Medical device balloons containing thermoplastic elastomers |
US5433706A (en) | 1993-10-25 | 1995-07-18 | Cordis Corporation | Perfusion balloon catheter |
US5425710A (en) | 1993-10-26 | 1995-06-20 | Medtronic, Inc. | Coated sleeve for wrapping dilatation catheter balloons |
US5417707A (en) | 1993-10-29 | 1995-05-23 | Medtronic, Inc. | Dilatation balloon protector with raised ribs |
US5350361A (en) | 1993-11-10 | 1994-09-27 | Medtronic, Inc. | Tri-fold balloon for dilatation catheter and related method |
US5545132A (en) | 1993-12-21 | 1996-08-13 | C. R. Bard, Inc. | Helically grooved balloon for dilatation catheter and method of using |
ATE261744T1 (en) | 1994-01-06 | 2004-04-15 | Scimed Life Systems Inc | BALLOON CATHETER WITH THERMOPLASTIC POLYIMIDE BALLOON |
US5792300A (en) | 1994-01-21 | 1998-08-11 | Cordis Corporation | Perfusion catheter and striped extrusion method of manufacture |
US6241734B1 (en) | 1998-08-14 | 2001-06-05 | Kyphon, Inc. | Systems and methods for placing materials into bone |
US20030032963A1 (en) | 2001-10-24 | 2003-02-13 | Kyphon Inc. | Devices and methods using an expandable body with internal restraint for compressing cancellous bone |
US6726691B2 (en) | 1998-08-14 | 2004-04-27 | Kyphon Inc. | Methods for treating fractured and/or diseased bone |
US7166121B2 (en) | 1994-01-26 | 2007-01-23 | Kyphon Inc. | Systems and methods using expandable bodies to push apart cortical bone surfaces |
NZ279442A (en) | 1994-01-26 | 1998-02-26 | Mark A Reiley | Bone treatment device; inflatable balloon for insertion into a bone; balloon details |
US6716216B1 (en) | 1998-08-14 | 2004-04-06 | Kyphon Inc. | Systems and methods for treating vertebral bodies |
US7044954B2 (en) | 1994-01-26 | 2006-05-16 | Kyphon Inc. | Method for treating a vertebral body |
US6248110B1 (en) | 1994-01-26 | 2001-06-19 | Kyphon, Inc. | Systems and methods for treating fractured or diseased bone using expandable bodies |
ATE361028T1 (en) | 1994-01-26 | 2007-05-15 | Kyphon Inc | IMPROVED INFLATABLE DEVICE FOR USE IN SURGICAL METHODS OF FIXATION OF BONE |
US5591129A (en) | 1994-03-02 | 1997-01-07 | Scimed Life Systems, Inc. | Perfusion balloon angioplasty catheter |
US5501667A (en) | 1994-03-15 | 1996-03-26 | Cordis Corporation | Perfusion balloon and method of use and manufacture |
US5819736A (en) | 1994-03-24 | 1998-10-13 | Sightline Technologies Ltd. | Viewing method and apparatus particularly useful for viewing the interior of the large intestine |
US5840064A (en) | 1994-03-31 | 1998-11-24 | United States Surgical Corporation | Method and apparatus for treating stenosis or other constriction in a bodily conduit |
US5556389A (en) | 1994-03-31 | 1996-09-17 | Liprie; Samuel F. | Method and apparatus for treating stenosis or other constriction in a bodily conduit |
US5599306A (en) | 1994-04-01 | 1997-02-04 | Localmed, Inc. | Method and apparatus for providing external perfusion lumens on balloon catheters |
DK63894A (en) | 1994-06-06 | 1996-01-08 | Meadox Medicals Inc | Stent catheter and method for making such a stent catheter |
US5513654A (en) | 1994-06-10 | 1996-05-07 | New Designs Corporation | Slip-resistant contraceptive male condom |
US5669879A (en) | 1994-06-15 | 1997-09-23 | Duer; Edward Yeend | Catheter assembly for dilation of constricted blood vessel |
US5458572A (en) | 1994-07-01 | 1995-10-17 | Boston Scientific Corp. | Catheter with balloon folding into predetermined configurations and method of manufacture |
US5470314A (en) | 1994-07-22 | 1995-11-28 | Walinsky; Paul | Perfusion balloon catheter with differential compliance |
US5554120A (en) | 1994-07-25 | 1996-09-10 | Advanced Cardiovascular Systems, Inc. | Polymer blends for use in making medical devices including catheters and balloons for dilatation catheters |
US5587125A (en) | 1994-08-15 | 1996-12-24 | Schneider (Usa) Inc. | Non-coextrusion method of making multi-layer angioplasty balloons |
US5567760A (en) | 1994-11-15 | 1996-10-22 | The Dow Chemical Company | Films from aqueous dispersions of block copolymers having hydrogenated conjugated diene block |
US5749851A (en) | 1995-03-02 | 1998-05-12 | Scimed Life Systems, Inc. | Stent installation method using balloon catheter having stepped compliance curve |
NL1000106C2 (en) | 1995-04-10 | 1996-10-11 | Cordis Europ | Balloon balloon balloon catheter and method of making the balloon. |
US5575771A (en) | 1995-04-24 | 1996-11-19 | Walinsky; Paul | Balloon catheter with external guidewire |
US5702373A (en) | 1995-08-31 | 1997-12-30 | Target Therapeutics, Inc. | Composite super-elastic alloy braid reinforced catheter |
US5623722A (en) | 1995-06-01 | 1997-04-22 | Xerox Corporation | Document set compiler and eject system |
US5647848A (en) | 1995-06-07 | 1997-07-15 | Meadox Medicals, Inc. | High strength low compliance composite balloon for balloon catheters |
US5865801A (en) | 1995-07-18 | 1999-02-02 | Houser; Russell A. | Multiple compartmented balloon catheter with external pressure sensing |
US5556382A (en) | 1995-08-29 | 1996-09-17 | Scimed Life Systems, Inc. | Balloon perfusion catheter |
US5868704A (en) | 1995-09-18 | 1999-02-09 | W. L. Gore & Associates, Inc. | Balloon catheter device |
GB2306111A (en) | 1995-10-14 | 1997-04-30 | William Barrie Hart | Expandable hydraulic oversleeve for advancing an endoscope into a body cavity |
FR2742652B1 (en) | 1995-12-21 | 1998-02-27 | Colorado | INTERVERTEBRAL IMPLANT, INTERSOMATIC CAGE TYPE |
US6099454A (en) | 1996-02-29 | 2000-08-08 | Scimed Life Systems, Inc. | Perfusion balloon and radioactive wire delivery system |
US5951458A (en) | 1996-02-29 | 1999-09-14 | Scimed Life Systems, Inc. | Local application of oxidizing agents to prevent restenosis |
US6234951B1 (en) | 1996-02-29 | 2001-05-22 | Scimed Life Systems, Inc. | Intravascular radiation delivery system |
IL117344A0 (en) | 1996-03-04 | 1996-07-23 | Lerner Alexander | Endoscopic device |
US6124007A (en) | 1996-03-06 | 2000-09-26 | Scimed Life Systems Inc | Laminate catheter balloons with additive burst strength and methods for preparation of same |
US5713867A (en) | 1996-04-29 | 1998-02-03 | Medtronic, Inc. | Introducer system having kink resistant splittable sheath |
US5718684A (en) | 1996-05-24 | 1998-02-17 | Gupta; Mukesh | Multi-lobed balloon catheter |
US6398776B1 (en) | 1996-06-03 | 2002-06-04 | Terumo Kabushiki Kaisha | Tubular medical device |
US6746425B1 (en) | 1996-06-14 | 2004-06-08 | Futuremed Interventional | Medical balloon |
US5749852A (en) | 1996-07-23 | 1998-05-12 | Medtronic, Inc. | Sheath system for autoperfusion dilatation catheter balloon |
US5735816A (en) | 1996-07-23 | 1998-04-07 | Medtronic, Inc. | Spiral sheath retainer for autoperfusion dilatation catheter balloon |
GB9616267D0 (en) | 1996-08-02 | 1996-09-11 | Ranier Ltd | Balloon catheter |
US5868707A (en) | 1996-08-15 | 1999-02-09 | Advanced Cardiovascular Systems, Inc. | Protective sheath for catheter balloons |
US5947924A (en) | 1996-09-13 | 1999-09-07 | Angiorad, L.L.C. | Dilatation/centering catheter used for the treatment of stenosis or other constriction in a bodily passageway and method thereof |
EP0835673A3 (en) | 1996-10-10 | 1998-09-23 | Schneider (Usa) Inc. | Catheter for tissue dilatation and drug delivery |
US6132368A (en) | 1996-12-12 | 2000-10-17 | Intuitive Surgical, Inc. | Multi-component telepresence system and method |
US5830181A (en) | 1997-02-07 | 1998-11-03 | Advanced Cardiovascular Systems, Inc. | Perfusion catheter with high flow distal tip |
WO1998036790A1 (en) | 1997-02-19 | 1998-08-27 | Condado Medical Devices Corporation | Multi-purpose catheters, catheter systems, and radiation treatment |
JPH10277157A (en) | 1997-04-02 | 1998-10-20 | Nippon Zeon Co Ltd | Balloon expansion catheter and manufacture thereof |
US6015421A (en) | 1997-05-15 | 2000-01-18 | General Surgical Innovations, Inc. | Apparatus and method for developing an anatomic space for laparoscopic procedures |
US6143015A (en) | 1997-05-19 | 2000-11-07 | Cardio Medical Solutions, Inc. | Device and method for partially occluding blood vessels using flow-through balloon |
US5972015A (en) | 1997-08-15 | 1999-10-26 | Kyphon Inc. | Expandable, asymetric structures for deployment in interior body regions |
EA001570B1 (en) | 1997-06-09 | 2001-04-23 | Кайфон Инк. | Systems and devices for treating gractured or deseased bones using expandable bodies, (alternatives), sterile kit of tools for insertion into bone (alternatives) |
US6048346A (en) | 1997-08-13 | 2000-04-11 | Kyphon Inc. | Systems and methods for injecting flowable materials into bones |
US5868779A (en) | 1997-08-15 | 1999-02-09 | Ruiz; Carlos E. | Apparatus and methods for dilating vessels and hollow-body organs |
US5968013A (en) | 1997-08-21 | 1999-10-19 | Scimed Life Systems, Inc. | Multi-function dilatation catheter |
US5968012A (en) | 1997-08-22 | 1999-10-19 | Scimed Lifesystems, Inc. | Balloon catheter with adjustable shaft |
US6183492B1 (en) | 1997-08-28 | 2001-02-06 | Charles C. Hart | Perfusion-isolation catheter apparatus and method |
US6284333B1 (en) | 1997-09-10 | 2001-09-04 | Scimed Life Systems, Inc. | Medical devices made from polymer blends containing low melting temperature liquid crystal polymers |
US6242063B1 (en) | 1997-09-10 | 2001-06-05 | Scimed Life Systems, Inc. | Balloons made from liquid crystal polymer blends |
WO1999013331A1 (en) | 1997-09-11 | 1999-03-18 | Shionogi & Co., Ltd. | Immunoassay method for bnp |
US5891114A (en) | 1997-09-30 | 1999-04-06 | Target Therapeutics, Inc. | Soft-tip high performance braided catheter |
LV12474B (en) | 1997-10-03 | 2001-01-20 | Sergejs Matasovs | Endoscope with single-use cartridge for invagination of endoscopic tube |
DE19748500B4 (en) | 1997-11-03 | 2006-03-30 | Stm Medizintechnik Starnberg Gmbh | Feed device for a flexible endoscope shaft |
IL122111A (en) | 1997-11-04 | 2004-06-01 | Sightline Techn Ltd | Video rectoscope |
US6645201B1 (en) | 1998-02-19 | 2003-11-11 | Curon Medical, Inc. | Systems and methods for treating dysfunctions in the intestines and rectum |
DE69914882T2 (en) | 1998-03-04 | 2004-12-16 | Boston Scientific Ltd., St. Michael | COMPOSITION AND METHOD FOR PRODUCING PBT CATHETER BALLOONS |
US6096054A (en) | 1998-03-05 | 2000-08-01 | Scimed Life Systems, Inc. | Expandable atherectomy burr and method of ablating an occlusion from a patient's blood vessel |
US6440138B1 (en) | 1998-04-06 | 2002-08-27 | Kyphon Inc. | Structures and methods for creating cavities in interior body regions |
US6338727B1 (en) | 1998-08-13 | 2002-01-15 | Alsius Corporation | Indwelling heat exchange catheter and method of using same |
US6190357B1 (en) | 1998-04-21 | 2001-02-20 | Cardiothoracic Systems, Inc. | Expandable cannula for performing cardiopulmonary bypass and method for using same |
DE29808180U1 (en) | 1998-05-06 | 1998-07-23 | Stm Medtech Starnberg | Drive device for slip hose system |
US6719773B1 (en) | 1998-06-01 | 2004-04-13 | Kyphon Inc. | Expandable structures for deployment in interior body regions |
ES2354492T3 (en) | 1998-06-01 | 2011-03-15 | Kyphon Sarl | PREFORMED STRUCTURES EXPANDABLE FOR DEPLOYMENT IN INTERNAL BODY REGIONS. |
FR2779644B1 (en) | 1998-06-11 | 2000-08-11 | Oreal | COSMETIC COMPOSITION COMPRISING AT LEAST ONE ADHESIVE POLYMER OF ACRYLIC OR METHACRYLIC ESTER |
US6036697A (en) | 1998-07-09 | 2000-03-14 | Scimed Life Systems, Inc. | Balloon catheter with balloon inflation at distal end of balloon |
US20050228397A1 (en) | 1998-08-14 | 2005-10-13 | Malandain Hugues F | Cavity filling device |
US6610083B2 (en) | 1998-08-24 | 2003-08-26 | Radiant Medical, Inc. | Multiple lumen heat exchange catheters |
GB9823492D0 (en) | 1998-10-27 | 1998-12-23 | Amba Med Ltd | Drape |
US7481803B2 (en) | 2000-11-28 | 2009-01-27 | Flowmedica, Inc. | Intra-aortic renal drug delivery catheter |
IL128286A (en) | 1999-01-29 | 2004-01-04 | Sightline Techn Ltd | Propulsion of a probe in the colon using a flexible sleeve |
US6905743B1 (en) | 1999-02-25 | 2005-06-14 | Boston Scientific Scimed, Inc. | Dimensionally stable balloons |
US6494862B1 (en) | 1999-07-13 | 2002-12-17 | Advanced Cardiovascular Systems, Inc. | Substance delivery apparatus and a method of delivering a therapeutic substance to an anatomical passageway |
CA2379670A1 (en) | 1999-08-12 | 2001-02-22 | Wilson-Cook Medical Inc. | Dilation balloon having multiple diameters |
US20040024465A1 (en) * | 1999-08-18 | 2004-02-05 | Gregory Lambrecht | Devices and method for augmenting a vertebral disc |
US6695809B1 (en) | 1999-09-13 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Catheter balloon with a discontinuous elastomeric outer layer |
US6977103B2 (en) | 1999-10-25 | 2005-12-20 | Boston Scientific Scimed, Inc. | Dimensionally stable balloons |
US6733513B2 (en) | 1999-11-04 | 2004-05-11 | Advanced Bioprosthetic Surfaces, Ltd. | Balloon catheter having metal balloon and method of making same |
GB9927711D0 (en) | 1999-11-24 | 2000-01-19 | Robinson Nicholas S | Vascular occluder |
US6652568B1 (en) | 1999-12-22 | 2003-11-25 | Advanced Cardiovascular Systems, Inc. | Radiopaque balloon |
CN1204937C (en) | 1999-12-24 | 2005-06-08 | 东丽株式会社 | Catheter with balloon |
US6450988B1 (en) | 1999-12-29 | 2002-09-17 | Advanced Cardiovascular Systems, Inc. | Centering catheter with improved perfusion |
US7163504B1 (en) | 2000-02-16 | 2007-01-16 | Advanced Cardiovascular Systems, Inc. | Multi-lumen fluted balloon radiation centering catheter |
US6756094B1 (en) | 2000-02-28 | 2004-06-29 | Scimed Life Systems, Inc. | Balloon structure with PTFE component |
US6554820B1 (en) | 2000-03-08 | 2003-04-29 | Scimed Life Systems, Inc. | Composite flexible tube for medical applications |
EP1277119A4 (en) | 2000-03-31 | 2006-09-06 | Siebel Systems Inc | Thin client method and system for generating page delivery language output from applets, views, and screen definitions |
EP1662972A4 (en) | 2000-04-03 | 2010-08-25 | Intuitive Surgical Inc | Activated polymer articulated instruments and methods of insertion |
US6837846B2 (en) | 2000-04-03 | 2005-01-04 | Neo Guide Systems, Inc. | Endoscope having a guide tube |
US7815649B2 (en) | 2000-04-07 | 2010-10-19 | Kyphon SÀRL | Insertion devices and method of use |
CN100396249C (en) | 2000-04-07 | 2008-06-25 | 科丰公司 | Insertion devices and method of use |
WO2001080935A1 (en) | 2000-04-21 | 2001-11-01 | Universite Pierre Et Marie Curie (Paris Vi) | Device for positioning, exploring and/or operating in particular in the field of endoscopy and/or minimally invasive surgery |
KR20020093109A (en) | 2000-05-02 | 2002-12-12 | 윌슨-쿡 메디컬 인크. | Introducer device for catheters o.t.l. with eversible sleeve |
EP1156021A1 (en) | 2000-05-19 | 2001-11-21 | Asahi Glass Co., Ltd. | Hollow aluminosilicate glass microspheres and process for their production |
US6663648B1 (en) | 2000-06-15 | 2003-12-16 | Cordis Corporation | Balloon catheter with floating stiffener, and procedure |
DE60117796T2 (en) | 2000-06-16 | 2006-11-30 | Abbott Laboratories, Abbott Park | BALLOONCLUSION DEVICE WITH A PROXIMAL VALVE |
US6875212B2 (en) | 2000-06-23 | 2005-04-05 | Vertelink Corporation | Curable media for implantable medical device |
KR100889414B1 (en) | 2000-06-27 | 2009-03-20 | 키폰 에스에이알엘 | Systems and methods for injecting flowable materials into bones |
CA2415389C (en) | 2000-07-14 | 2009-02-17 | Kyphon Inc. | Systems and methods for treating vertebral bodies |
US20080086133A1 (en) | 2003-05-16 | 2008-04-10 | Spineology | Expandable porous mesh bag device and methods of use for reduction, filling, fixation and supporting of bone |
AU2001282959A1 (en) | 2000-07-24 | 2002-02-05 | Jeffrey Grayzel | Stiffened balloon catheter for dilatation and stenting |
IL138237A (en) | 2000-09-04 | 2008-12-29 | Stryker Gi Ltd | Double sleeve endoscope |
AU2002211639A1 (en) | 2000-10-09 | 2002-04-22 | Tricardia, L.L.C. | Material useable for medical balloons and catheters |
CA2426688C (en) | 2000-10-25 | 2011-12-20 | Kyphon Inc. | Systems and methods for reducing fractured bone using a fracture reduction cannula |
US6623504B2 (en) | 2000-12-08 | 2003-09-23 | Scimed Life Systems, Inc. | Balloon catheter with radiopaque distal tip |
US20030078539A1 (en) | 2000-12-27 | 2003-04-24 | Peterson Eric D. | Perfusion catheter and membrane |
US6629952B1 (en) | 2000-12-29 | 2003-10-07 | Scimed Life Systems, Inc. | High pressure vascular balloon catheter |
US6752829B2 (en) | 2001-01-30 | 2004-06-22 | Scimed Life Systems, Inc. | Stent with channel(s) for containing and delivering a biologically active material and method for manufacturing the same |
US20020161388A1 (en) | 2001-02-27 | 2002-10-31 | Samuels Sam L. | Elastomeric balloon support fabric |
WO2002076700A1 (en) | 2001-03-26 | 2002-10-03 | Machine Solutions, Inc. | Balloon folding technology |
US6632235B2 (en) | 2001-04-19 | 2003-10-14 | Synthes (U.S.A.) | Inflatable device and method for reducing fractures in bone and in treating the spine |
US6783524B2 (en) | 2001-04-19 | 2004-08-31 | Intuitive Surgical, Inc. | Robotic surgical tool with ultrasound cauterizing and cutting instrument |
US6796960B2 (en) | 2001-05-04 | 2004-09-28 | Wit Ip Corporation | Low thermal resistance elastic sleeves for medical device balloons |
US6911038B2 (en) | 2001-05-08 | 2005-06-28 | Scimed Life Systems, Inc. | Matched balloon to stent shortening |
US6651659B2 (en) | 2001-05-23 | 2003-11-25 | John I. Izuchukwu | Ambulatory storage system for pressurized gases |
JP2002360700A (en) | 2001-06-04 | 2002-12-17 | Japan Lifeline Co Ltd | Balloon catheter and method of manufacturing balloon for balloon catheter |
US6679860B2 (en) | 2001-06-19 | 2004-01-20 | Medtronic Ave, Inc. | Intraluminal therapy catheter with inflatable helical member and methods of use |
US6605056B2 (en) | 2001-07-11 | 2003-08-12 | Scimed Life Systems, Inc. | Conformable balloon |
US20030050644A1 (en) | 2001-09-11 | 2003-03-13 | Boucher Ryan P. | Systems and methods for accessing and treating diseased or fractured bone employing a guide wire |
JP2003117002A (en) | 2001-10-10 | 2003-04-22 | Japan Lifeline Co Ltd | Balloon, balloon catheter and method of manufacturing the same |
JP4499327B2 (en) | 2001-12-06 | 2010-07-07 | 松崎 浩巳 | Diameter expansion instrument and surgical instrument set |
US7037562B2 (en) | 2002-01-14 | 2006-05-02 | Vascon Llc | Angioplasty super balloon fabrication with composite materials |
DE60326699D1 (en) | 2002-01-28 | 2009-04-30 | Orbusneich Medical Inc | EXPANDED OSTIUM DOPROTHESIS AND FEEDING SYSTEM |
US7029732B2 (en) | 2002-02-28 | 2006-04-18 | Boston Scientific Scimed, Inc. | Medical device balloons with improved strength properties and processes for producing same |
US6946173B2 (en) | 2002-03-21 | 2005-09-20 | Advanced Cardiovascular Systems, Inc. | Catheter balloon formed of ePTFE and a diene polymer |
US7723434B2 (en) | 2002-03-27 | 2010-05-25 | Nof Corporation | Olefinic thermoplastic elastomer and moldings thereof |
US6743463B2 (en) | 2002-03-28 | 2004-06-01 | Scimed Life Systems, Inc. | Method for spray-coating a medical device having a tubular wall such as a stent |
US20030236495A1 (en) | 2002-05-16 | 2003-12-25 | Kennedy Kenneth C. | Non-buckling balloon catheter |
US6773447B2 (en) | 2002-07-02 | 2004-08-10 | Sentient Engineering & Technology, Llc | Balloon catheter and treatment apparatus |
US7335184B2 (en) | 2002-07-02 | 2008-02-26 | Sentient Engineering And Technology | Balloon catheter and treatment apparatus |
US7166120B2 (en) | 2002-07-12 | 2007-01-23 | Ev3 Inc. | Catheter with occluding cuff |
US6878329B2 (en) | 2002-07-30 | 2005-04-12 | Advanced Cardiovascular Systems, Inc. | Method of making a catheter balloon using a polyimide covered mandrel |
JP4351832B2 (en) | 2002-08-05 | 2009-10-28 | テルモ株式会社 | Balloon catheter |
JP2005535403A (en) | 2002-08-15 | 2005-11-24 | サイトライン テクノロジーズ リミテッド | Endoscope sleeve dispenser |
JP2006508776A (en) | 2002-09-20 | 2006-03-16 | フローメディカ,インコーポレイテッド | Method and apparatus for selective substance delivery via an intrarenal catheter |
US7488337B2 (en) | 2002-09-30 | 2009-02-10 | Saab Mark A | Apparatus and methods for bone, tissue and duct dilatation |
JP2006500986A (en) | 2002-09-30 | 2006-01-12 | サイトライン テクノロジーズ リミテッド | Endoscopic tool driven by piston |
US20040061261A1 (en) | 2002-09-30 | 2004-04-01 | Fernando Gonzalez | Method of making a catheter balloon using a heated mandrel |
US7837669B2 (en) | 2002-11-01 | 2010-11-23 | Valentx, Inc. | Devices and methods for endolumenal gastrointestinal bypass |
US20050004515A1 (en) | 2002-11-15 | 2005-01-06 | Hart Charles C. | Steerable kink resistant sheath |
US6945957B2 (en) | 2002-12-30 | 2005-09-20 | Scimed Life Systems, Inc. | Valve treatment catheter and methods |
US7081096B2 (en) | 2003-01-24 | 2006-07-25 | Medtronic Vascular, Inc. | Temperature mapping balloon |
US6951675B2 (en) | 2003-01-27 | 2005-10-04 | Scimed Life Systems, Inc. | Multilayer balloon catheter |
US20060195005A1 (en) | 2003-02-14 | 2006-08-31 | Koichi Sakai | Balloon for intraaortic balloon pumping catheter, catheter fitted with the same, and process for producing the balloon |
US7252605B2 (en) | 2003-02-21 | 2007-08-07 | Snider James L | Articulated football goal including sacrificial crossbar |
US7438712B2 (en) | 2003-03-05 | 2008-10-21 | Scimed Life Systems, Inc. | Multi-braid exterior tube |
IL156381A0 (en) | 2003-06-10 | 2004-01-04 | Sightline Techn Ltd | Garment for patients in endoscopy |
US7011646B2 (en) | 2003-06-24 | 2006-03-14 | Advanced Cardiovascular Systems, Inc. | Balloon catheter having a balloon with a thickened wall portion |
US7727442B2 (en) | 2003-07-10 | 2010-06-01 | Boston Scientific Scimed, Inc. | Medical device tubing with discrete orientation regions |
US7744620B2 (en) | 2003-07-18 | 2010-06-29 | Intervalve, Inc. | Valvuloplasty catheter |
US6908428B2 (en) | 2003-09-04 | 2005-06-21 | Sightline Technologies Ltd. | Sleeve for endoscopic tools |
US20050209674A1 (en) | 2003-09-05 | 2005-09-22 | Kutscher Tuvia D | Balloon assembly (V) |
EP1677849A1 (en) | 2003-10-14 | 2006-07-12 | Cube Medical A/S | A balloon for use in angioplasty |
US20050082965A1 (en) | 2003-10-16 | 2005-04-21 | Chiao-Chiang Huang | LED with good heat-dissipating capability |
US20050123702A1 (en) | 2003-12-03 | 2005-06-09 | Jim Beckham | Non-compliant medical balloon having a longitudinal fiber layer |
US7273471B1 (en) | 2003-12-23 | 2007-09-25 | Advanced Cardiovascular Systems, Inc. | Catheter balloon having a porous layer with ridges |
WO2005072804A1 (en) | 2004-01-28 | 2005-08-11 | Cook Critical Care Incorproated | Dilational device having a reinforced balloon catheter |
ES2407684T3 (en) | 2004-05-05 | 2013-06-13 | Direct Flow Medical, Inc. | Heart valve without stent with support structure formed on site |
US7758892B1 (en) | 2004-05-20 | 2010-07-20 | Boston Scientific Scimed, Inc. | Medical devices having multiple layers |
US20050271844A1 (en) | 2004-06-07 | 2005-12-08 | Scimed Life Systems, Inc. | Artificial silk reinforcement of PTCA balloon |
US7635510B2 (en) | 2004-07-07 | 2009-12-22 | Boston Scientific Scimed, Inc. | High performance balloon catheter/component |
DE602005005567T2 (en) | 2004-07-28 | 2009-04-30 | Cordis Corp., Miami Lakes | Insertion device with a low deployment force |
WO2006016299A1 (en) | 2004-08-09 | 2006-02-16 | Koninklijke Philips Electronics N.V. | Integrated f-class amplifier with output parasitic capacitance compensation |
WO2006034396A2 (en) | 2004-09-21 | 2006-03-30 | Stout Medical Group, L.P. | Balloon and methods of making and using |
US7491188B2 (en) | 2004-10-12 | 2009-02-17 | Boston Scientific Scimed, Inc. | Reinforced and drug-eluting balloon catheters and methods for making same |
US7309324B2 (en) | 2004-10-15 | 2007-12-18 | Futuremed Interventional, Inc. | Non-compliant medical balloon having an integral woven fabric layer |
US7354419B2 (en) | 2004-10-15 | 2008-04-08 | Futuremed Interventional, Inc. | Medical balloon having strengthening rods |
US7914487B2 (en) | 2004-10-15 | 2011-03-29 | Futurematrix Interventional, Inc. | Non-compliant medical balloon having braided or knitted reinforcement |
US7682335B2 (en) | 2004-10-15 | 2010-03-23 | Futurematrix Interventional, Inc. | Non-compliant medical balloon having an integral non-woven fabric layer |
JP5006204B2 (en) | 2004-11-15 | 2012-08-22 | カイフォン・ソシエテ・ア・レスポンサビリテ・リミテ | Apparatus comprising an inflatable structure configured for insertion into a skeletal support structure |
US7879053B2 (en) | 2004-12-20 | 2011-02-01 | Boston Scientific Scimed, Inc. | Balloon with stepped sections and implements |
US20060149131A1 (en) | 2005-01-05 | 2006-07-06 | Sightline Technologies Ltd. | Surgical tool for endoscope |
US20060149128A1 (en) | 2005-01-05 | 2006-07-06 | Sightline Technologies Ltd. | Method and devices for lubricating an endoscopic surgical tool |
WO2006086516A2 (en) | 2005-02-09 | 2006-08-17 | Angiodynamics, Inc. | Reinforced balloon for a catheter |
US20090012500A1 (en) | 2005-02-10 | 2009-01-08 | Kaneka Corporation | Medical Catheter Tube and Method of Producing the Same |
US20060183974A1 (en) | 2005-02-14 | 2006-08-17 | Sightline Technologies Ltd. | Endoscope With Improved Maneuverability |
US8048028B2 (en) | 2005-02-17 | 2011-11-01 | Boston Scientific Scimed, Inc. | Reinforced medical balloon |
JP2008531123A (en) | 2005-02-25 | 2008-08-14 | ジンテス ゲゼルシャフト ミット ベシュレンクテル ハフツング | Resorbable containment device and its manufacturing and use processes |
US20060195135A1 (en) | 2005-02-25 | 2006-08-31 | Ihab Ayoub | Pass-through catheter |
US20060224113A1 (en) | 2005-03-31 | 2006-10-05 | Van Sloten Leonard A | Esophageal balloon catheter with asymmetrical balloon |
US20060235457A1 (en) | 2005-04-15 | 2006-10-19 | Amir Belson | Instruments having a rigidizable external working channel |
US20060252989A1 (en) | 2005-05-04 | 2006-11-09 | Sightline Technologies Ltd. | Endoscopic apparatus provided with inflatable propelling sleeve |
US8672990B2 (en) | 2005-05-27 | 2014-03-18 | Boston Scientific Scimed, Inc. | Fiber mesh controlled expansion balloon catheter |
US7500982B2 (en) | 2005-06-22 | 2009-03-10 | Futurematrix Interventional, Inc. | Balloon dilation catheter having transition from coaxial lumens to non-coaxial multiple lumens |
US7691082B2 (en) | 2005-07-01 | 2010-04-06 | Boston Scientific Scimed, Inc. | Medical devices |
US7544201B2 (en) | 2005-07-05 | 2009-06-09 | Futurematrix Interventional, Inc. | Rapid exchange balloon dilation catheter having reinforced multi-lumen distal portion |
US20070010844A1 (en) | 2005-07-08 | 2007-01-11 | Gorman Gong | Radiopaque expandable body and methods |
US8052637B2 (en) | 2005-07-12 | 2011-11-08 | Abbott Laboratories | Medical device balloon |
US20070043262A1 (en) | 2005-08-18 | 2007-02-22 | Sightline Technologies Ltd. | Fluid supply for endoscope |
EP1921977A2 (en) | 2005-09-06 | 2008-05-21 | Stryker GI Ltd | Disposable cap for endoscope |
US8876763B2 (en) | 2005-11-01 | 2014-11-04 | Boston Scientific Scimed, Inc. | Composite balloon |
US20070100279A1 (en) | 2005-11-03 | 2007-05-03 | Paragon Intellectual Properties, Llc | Radiopaque-balloon microcatheter and methods of manufacture |
US20070112300A1 (en) | 2005-11-14 | 2007-05-17 | Roman Ricardo D | Balloon folding design, apparatus and method of making the same |
EP2269810A3 (en) | 2005-11-14 | 2013-07-31 | Abbott Laboratories Vascular Enterprises Limited | Medical device |
US20070112250A1 (en) | 2005-11-16 | 2007-05-17 | Yasuhito Kura | Insertion support tool for medical instrument and insertion method for medical instrument |
EP1968686B1 (en) | 2005-12-16 | 2019-05-08 | Confluent Medical Technologies, Inc. | Multi-layer balloons for medical applications |
US8585753B2 (en) | 2006-03-04 | 2013-11-19 | John James Scanlon | Fibrillated biodegradable prosthesis |
US20070225800A1 (en) | 2006-03-24 | 2007-09-27 | Sahatjian Ronald A | Methods and devices having electrically actuatable surfaces |
US20070244501A1 (en) | 2006-04-18 | 2007-10-18 | Horn Daniel J | Medical balloons |
US8187297B2 (en) | 2006-04-19 | 2012-05-29 | Vibsynt, Inc. | Devices and methods for treatment of obesity |
US8858855B2 (en) | 2006-04-20 | 2014-10-14 | Boston Scientific Scimed, Inc. | High pressure balloon |
US20070265565A1 (en) | 2006-05-15 | 2007-11-15 | Medtronic Vascular, Inc. | Mesh-Reinforced Catheter Balloons and Methods for Making the Same |
US20070270688A1 (en) | 2006-05-19 | 2007-11-22 | Daniel Gelbart | Automatic atherectomy system |
US7943221B2 (en) | 2006-05-22 | 2011-05-17 | Boston Scientific Scimed, Inc. | Hinged compliance fiber braid balloon |
US20070286982A1 (en) | 2006-06-12 | 2007-12-13 | Higgins Kenneth B | Surface coverings and methods |
US8979886B2 (en) | 2006-08-07 | 2015-03-17 | W. L. Gore & Associates, Inc. | Medical balloon and method of making the same |
US20080097374A1 (en) | 2006-08-07 | 2008-04-24 | Korleski Joseph E | Inflatable shaped balloons |
US7785290B2 (en) | 2006-08-07 | 2010-08-31 | Gore Enterprise Holdings, Inc. | Non-shortening high angle wrapped balloons |
US20080140173A1 (en) | 2006-08-07 | 2008-06-12 | Sherif Eskaros | Non-shortening wrapped balloon |
US20080125711A1 (en) | 2006-08-07 | 2008-05-29 | Alpini Alfred A | Catheter balloons with integrated non-distensible seals |
US20080097300A1 (en) | 2006-08-07 | 2008-04-24 | Sherif Eskaros | Catheter balloon with multiple micropleats |
US7691080B2 (en) | 2006-09-21 | 2010-04-06 | Mercator Medsystems, Inc. | Dual modulus balloon for interventional procedures |
EP2711045B1 (en) | 2006-10-12 | 2018-06-13 | C. R. Bard, Inc. | Inflatable structure with braided layer |
US7828055B2 (en) | 2006-10-17 | 2010-11-09 | Baker Hughes Incorporated | Apparatus and method for controlled deployment of shape-conforming materials |
US7762985B2 (en) | 2006-11-01 | 2010-07-27 | Cook Incorporated | Balloon catheter for treating hardened lesions |
US7811284B2 (en) * | 2006-11-10 | 2010-10-12 | Illuminoss Medical, Inc. | Systems and methods for internal bone fixation |
US8153181B2 (en) | 2006-11-14 | 2012-04-10 | Boston Scientific Scimed, Inc. | Medical devices and related methods |
US7641844B2 (en) | 2006-12-11 | 2010-01-05 | Cook Incorporated | Method of making a fiber-reinforced medical balloon |
ES2510675T3 (en) | 2006-12-18 | 2014-10-21 | C.R. Bard, Inc. | Balloon with dividing fabric layers and method for braiding on three-dimensional shapes |
US7753875B2 (en) | 2007-01-24 | 2010-07-13 | Cook Incorporated | Preform and balloon having a non-uniform thickness |
US20080183038A1 (en) | 2007-01-30 | 2008-07-31 | Loma Vista Medical, Inc. | Biological navigation device |
WO2008095052A2 (en) | 2007-01-30 | 2008-08-07 | Loma Vista Medical, Inc., | Biological navigation device |
US10278682B2 (en) | 2007-01-30 | 2019-05-07 | Loma Vista Medical, Inc. | Sheaths for medical devices |
US20080228139A1 (en) | 2007-02-06 | 2008-09-18 | Cook Incorporated | Angioplasty Balloon With Concealed Wires |
CN101743032B (en) | 2007-03-27 | 2012-09-19 | 因特拉泰克医药有限公司 | Spiral balloon catheter |
US20080255512A1 (en) | 2007-04-10 | 2008-10-16 | Medtronic Vascular, Inc. | Balloons Having Improved Strength and Methods for Making Same |
US7833218B2 (en) | 2007-04-17 | 2010-11-16 | Medtronic Vascular, Inc. | Catheter with reinforcing layer having variable strand construction |
US9308086B2 (en) | 2010-09-21 | 2016-04-12 | Hocor Cardiovascular Technologies Llc | Method and system for balloon counterpulsation during aortic valve replacement |
US8313601B2 (en) | 2007-08-06 | 2012-11-20 | Bard Peripheral Vascular, Inc. | Non-compliant medical balloon |
US8002744B2 (en) | 2007-08-06 | 2011-08-23 | Bard Peripheral Vascular, Inc | Non-compliant medical balloon |
WO2009040610A1 (en) | 2007-09-26 | 2009-04-02 | Fitt S.P.A. | High flexibility hose structure for high pressure apparatus, and method for making same |
US20090099517A1 (en) | 2007-10-10 | 2009-04-16 | C. R. Bard, Inc. | Reinforced, non-compliant angioplasty balloon |
WO2009052838A1 (en) | 2007-10-24 | 2009-04-30 | Wael Mohamed Nabil Lotfy | Perfusion balloon catheter |
US8075519B2 (en) | 2007-12-06 | 2011-12-13 | Abbott Cardiovascular Systems Inc. | Agent delivery catheter having a radially expandable centering support members |
DE102008006092A1 (en) | 2008-01-25 | 2009-07-30 | Biotronik Vi Patent Ag | Multiple membrane balloon and method of making a multiple membrane balloon |
US8034022B2 (en) | 2008-04-08 | 2011-10-11 | Cook Medical Technologies Llc | Weeping balloon catheter |
EP2278908B1 (en) | 2008-04-27 | 2021-06-02 | Loma Vista Medical, Inc. | Biological navigation device |
US8182510B2 (en) | 2008-05-30 | 2012-05-22 | Lisa Ann Brabant | Sterling silver and/or metal gel and/or liquid centered teether |
WO2009149108A1 (en) | 2008-06-02 | 2009-12-10 | Loma Vista Medical, Inc. | Inflatable medical devices |
EP2147695B1 (en) | 2008-07-23 | 2011-11-30 | Abbott Laboratories Vascular Enterprises Limited | Balloon of a balloon catheter |
US20100042198A1 (en) | 2008-08-18 | 2010-02-18 | Burton David G | Single piece double wall dilation balloon catheter |
US10806907B2 (en) | 2008-09-05 | 2020-10-20 | C.R. Bard, Inc. | Balloon with radiopaque adhesive |
US20100234875A1 (en) | 2008-10-30 | 2010-09-16 | R4 Vascular, Inc. | Rupture-resistant compliant radiopaque catheter balloon and methods for use of same in an intravascular surgical procedure |
WO2010079494A1 (en) | 2009-01-12 | 2010-07-15 | Angioslide Ltd. | Balloon and catheter system and methods for making and use thereof |
US8900215B2 (en) | 2009-06-12 | 2014-12-02 | Bard Peripheral Vascular, Inc. | Semi-compliant medical balloon |
US8236223B2 (en) | 2009-07-02 | 2012-08-07 | C.R. Bard, Inc. | Checker balloon winding machine |
US9126022B2 (en) | 2009-08-24 | 2015-09-08 | Cook Medical Technologies Llc | Textile-reinforced high-pressure balloon |
US9211391B2 (en) | 2009-09-24 | 2015-12-15 | Bard Peripheral Vascular, Inc. | Balloon with variable pitch reinforcing fibers |
US20110087191A1 (en) | 2009-10-14 | 2011-04-14 | Boston Scientific Scimed, Inc. | Balloon catheter with shape memory sheath for delivery of therapeutic agent |
EP2512375B1 (en) | 2009-12-15 | 2016-12-07 | Edwards Lifesciences Corporation | Expansion device for treatment of vascular passageways |
EP2528540A4 (en) | 2010-01-29 | 2013-11-13 | Icon Medical Corp | Biodegradable protrusions on inflatable device |
US20110190727A1 (en) | 2010-02-02 | 2011-08-04 | Boston Scientific Scimed, Inc. | Intervascular catheter, system and method |
EP2616130A1 (en) | 2010-09-13 | 2013-07-24 | Intervalve, Inc. | Positionable valvuloplasty catheter |
US9480823B2 (en) | 2011-03-04 | 2016-11-01 | Medtronic Vascular, Inc. | Perfusion dilation catheter system and methods of use |
USD703515S1 (en) * | 2013-01-22 | 2014-04-29 | Tyto Life LLC | Cover panel for frame based door lock |
-
2011
- 2011-11-09 US US13/293,058 patent/US10188436B2/en active Active
-
2019
- 2019-01-07 US US16/241,220 patent/US10966763B2/en active Active
Patent Citations (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US833044A (en) * | 1906-03-13 | 1906-10-09 | Claudius Ash Sons & Company 1905 Ltd | Dental instrument. |
US1469004A (en) * | 1920-03-05 | 1923-09-25 | Holtz Gustav | Amalgam carrier and plugger |
US3724076A (en) * | 1971-04-05 | 1973-04-03 | Vac O Cast | Dental cement gun |
US4215985A (en) * | 1977-09-13 | 1980-08-05 | Establissement Dentaire Ivoclar | Mixing container |
US4431414A (en) * | 1982-01-25 | 1984-02-14 | Lawrence John S | Dental syringe for filling cavities in teeth |
US4769011A (en) * | 1985-03-28 | 1988-09-06 | Interpore International, Inc. | Syringe apparatus and method for the surgical implantation of granular substances |
US4757827A (en) * | 1987-02-17 | 1988-07-19 | Versaflex Delivery Systems Inc. | Steerable guidewire with deflectable tip |
US5637092A (en) * | 1995-01-30 | 1997-06-10 | Shaw; Thomas J. | Syringe plunger locking assembly |
US5849014A (en) * | 1997-03-20 | 1998-12-15 | Johnson & Johnson Professional, Inc. | Cement restrictor system and method of forming a cement plug within the medullary canal of a bone |
US6348055B1 (en) * | 1999-03-24 | 2002-02-19 | Parallax Medical, Inc. | Non-compliant system for delivery of implant material |
US6730095B2 (en) * | 2002-06-26 | 2004-05-04 | Scimed Life Systems, Inc. | Retrograde plunger delivery system |
US20050070915A1 (en) * | 2003-09-26 | 2005-03-31 | Depuy Spine, Inc. | Device for delivering viscous material |
US20070162042A1 (en) * | 2003-11-18 | 2007-07-12 | Thomas Dunker | Injection pump |
US20060259006A1 (en) * | 2005-04-29 | 2006-11-16 | Mckay William F | Devices and methods for delivering medical agents |
US20100056989A1 (en) * | 2005-04-29 | 2010-03-04 | Warsaw Orthopedic, Inc. | Instrumentation for injection of therapeutic fluid into joints |
US7513901B2 (en) * | 2005-05-19 | 2009-04-07 | Warsaw Orthopedic, Inc. | Graft syringe assembly |
US20070233146A1 (en) * | 2006-01-27 | 2007-10-04 | Stryker Corporation | Low pressure delivery system and method for delivering a solid and liquid mixture into a target site for medical treatment |
US8062254B2 (en) * | 2008-01-08 | 2011-11-22 | MacLean, LLC | Spring driven adjustable oral syringe |
US20110034885A1 (en) * | 2009-08-05 | 2011-02-10 | The University Of Toledo | Needle for directional control of the injection of bone cement into a vertebral compression fracture |
Cited By (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20190008566A1 (en) * | 2001-11-03 | 2019-01-10 | DePuy Synthes Products, Inc. | Device for straightening and stabilizing the vertebral column |
US11051862B2 (en) * | 2001-11-03 | 2021-07-06 | DePuy Synthes Products, Inc. | Device for straightening and stabilizing the vertebral column |
US10188273B2 (en) | 2007-01-30 | 2019-01-29 | Loma Vista Medical, Inc. | Biological navigation device |
US20110060186A1 (en) * | 2008-04-27 | 2011-03-10 | Alexander Quillin Tilson | Biological navigation device |
US8708955B2 (en) | 2008-06-02 | 2014-04-29 | Loma Vista Medical, Inc. | Inflatable medical devices |
US9186488B2 (en) | 2008-06-02 | 2015-11-17 | Loma Vista Medical, Inc. | Method of making inflatable medical devices |
US9504811B2 (en) | 2008-06-02 | 2016-11-29 | Loma Vista Medical, Inc. | Inflatable medical devices |
US9592119B2 (en) | 2010-07-13 | 2017-03-14 | C.R. Bard, Inc. | Inflatable medical devices |
CN103908332A (en) * | 2013-01-09 | 2014-07-09 | 上海凯利泰医疗科技股份有限公司 | Equipment for injecting bone cement |
US9730707B2 (en) | 2014-08-20 | 2017-08-15 | Kyphon SÀRL | Surgical instrument with graduated markings correlating to angulation |
CN113827352A (en) * | 2021-09-17 | 2021-12-24 | 海南医学院 | Dental pile drives with oral cavity prosthetic devices |
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US20190133649A1 (en) | 2019-05-09 |
US10966763B2 (en) | 2021-04-06 |
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